Note : Les descriptions sont présentées dans la langue officielle dans laquelle elles ont été soumises.
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BIOCERAMIC COMPOSITIONS
Background of the Invention
Much research in the area of biopharmaceutics is directed toward the
development
of effective implantable vehicles for drug delivery and other surgical
applications. Such
vehicles must be biocompatible and also must be capable of protecting the
activity of any
biologically active agent they are intended to deliver. Many biologically
active agents are
labile and easily lose activity when they are incorporated into a delivery
material.
Preservation of protein activity has posed particularly difficult problems.
In the drug delivery arena, calcium phosphate ceramics have been studied as
potential delivery vehicles due to their well known biocompatibility and their
affinity for
protein reagents (see, for example, IJntema et al., Int. J. Pharm. 112:215,
1994; Itokazu
et al., J. Orth. Surg. 2:47, 1994; Shinto et al., J. Bone Joint Surg. 74-
B:600, 1992;
Uchida et al., J. Orth. Res. 10:440, 1992). However, the reactions employed to
produce
known calcium phosphate ceramic materials typically require elevated
temperatures and/or
pressures, and also require the presence of acids or bases. Because most
biologically
active agents would be destroyed by one or more of the conditions required to
produce
the ceramic, the biologically active agents can only be loaded in after the
material is
produced, which can limit the amount and type of agent that can be delivered.
Also, although a number of calcium phosphate materials have been referred to
as
"resorbable", such compounds, usually comprising or derived from tricalcium
phosphate,
tetracalcium phosphate or hydroxyapatite are in fact only weakly resorbable.
Of the
group, the tricalcium phosphate compounds have been demonstrated to be the
most
resorbable and, after many years of study, they are still not widely used in
clinical
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settings. The tricalcium phosphates are known to have lengthy and somewhat
unpredictable resorption profiles, generally requiring in excess of one year
for resorption.
Unless steps are taken to produce extremely porous or channeled tricalcium
phosphates,
these compounds are not replaced by bone. Recent studies have lead to the
conclusion
that the "biodegradation of TCP, which is higher than that of
[hydroxyapatite], is not
sufficient" (Berger et al., Biomaterials, 16:1241, 1995).
Tetracalcium phosphate and hydroxyapatite derived compounds are also only
weakly resorbable. Published reports of tetracalcium phosphate fillers
generally describe
partial resorption over long periods of time. For example, as reported by
Horioglu et al.,
it is not uncommon for such materials to require 30 months for 80% resorption
(Soc. for
Biomaterials, pg. 198, March 18-22, 1995). Also, many reports that describe
"resorption" of calcium phosphate materials do not actually demonstrate
resorption
because the authors do not rule out, for example, migration of the vehicle
from the
implant site (see, for example, IJntema et al., supra).
In the surgical arena, One of the goals of reconstructive surgery is to be
able to
replace damaged tissue with new tissue, perhaps grown from a patient's own
cells. For
example, researchers have endeavored to develop cartilage regeneration systems
in which
isolated chondrocytes are injected into a damaged area in the context of a
polymer
scaffold (see, for example, Atala et al., J. Urol. 150:747, 1993; Freed et
al., J. Cell.
Biochem. 51:257, 1993 and references cited therein). Similar seeded scaffold
systems
have been studied in the context of bone repair, where osteoblast cells are
utilized in
conjunction with polymeric or ceramic supports (see, for example, Elgendy et
al.,
Biomater. 14:263, 1993; Ishaug et al., J. Biomed. Mater. Res. 28:1445, 1994).
Seeded
compositions have also been studied for their utility in bladder control and
vesicoureteral
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applications (see, for example, Griffith-Cima et al., published PCT
application no. WO
94/25080.
Researchers in the field have identified several characteristics that are
desirable for
scaffold materials to be used in such seeded compositions. For example, Freed
et al.
(Bio/Technology 12:689, 1994) list the following six factors as desirable
features:
(1) the scaffold surface should permit cell adhesion and growth;
(2) neither the scaffold material nor its degradation products should provoke
inflammation or toxicity when implanted in vivo;
(3) the scaffold material should be reproducibly processable into three
dimensional structures;
(4) the scaffold material should have a porosity of at least 90% so that it
provides high surface area for cell-scaffold interactions, sufficient space
for
extracellular matrix regeneration, and minimal diffusion constraints during
in vitro culture;
(5) the scaffold material should resorb once it has served its purpose of
providing a template for the regenerating tissue; and
(6) the scaffold degradation rate should be adjustable to match the rate of
tissue
regeneration by the cell type of interest.
There remains a need for the development of a drug delivery vehicle that is
biocompatible, fully resorbable, and not detrimental to drug activity. There
is also a need
to develop suitable materials for use as scaffolds in tissue repair. The
present invention
solves these needs, providing materials and compositions useful in drug
delivery and in
tissue repair.
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_..... .~..... . ..~.~~..,_...._.~.~.~~.,,._,~--... _. _ . .......... ........
. . M ..._... ..~.-..... .._..W...-......_ __ __ _._ __
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Definitions
"Amorphous "-- By "amorphous" as that term is used here, it is meant a
material
with significant amorphous character. Significant amorphous character
contemplates
greater than 75% amorphous content, preferably greater than 90% amorphous
content,
and is characterized by a broad, featureless X-ray diffraction pattern. It is
recognized
that a small degree of crystallinity may exist in the material. However, for
the
amorphous precursor materials of the present invention, it is preferable that
the degree of
crystallinity be less than that desired in the product material.
"Bioactive"-- "Bioactive" refers to a material that induces hard tissue
formation in
and about the implant. When implanted in soft tissue, the bioactivity may also
require the
presence of a growth or trophic factor, or the seeding of the implant with a
hard tissue
forming cell type.
"Biocompatible"-- The term "biocompatible", as used herein, means that the
material does not elicit a substantial detrimental response in the host. There
is always
concern, when a foreign object is introduced into a living body, that the
object will
induce an immune reaction, such as an inflammatory response that will have
negative
effects on the host. For example, although hydroxyapatite is generally
considered to be
"biocompatible", significant inflammation and tissue necrosis have been
observed when
crystalline hydroxyapatite microcarriers are inserted intramuscularly in
animals (see, for
example, IJntema et al., Int. J. Pharm 112:215 (1994)).
"Bioresorbable"-- "Bioresorbable" refers to the ability of a material to be
resorbed in vivo. "Full" resorption means that no significant extracellular
fragments
remain. The resorption process involves elimination of the original implant
materials
through the action of body fluids, enzymes or cells. Resorbed calcium
phosphate may,
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for example, be redeposited as bone mineral, or by being otherwise reutilized
within the
body, or excreted. "Strongly bioresorbable", as that term is used herein,
means that at
least 80%, preferably 95-99%, and most preferably >99%, of the total mass of
trraterial
implanted intramuscularly or subcutaneously is resorbed within one year. In
preferred
embodiments of the invention, the strongly resorbing poorly crystalline
apatitic (PCA)
calcium phosphate is characterized in that, when at least 1 g (preferably 1-5
g) of PCA
material is implanted at a subcutaneous or intramuscular site, at least 80% of
the material
is resorbed within one year. In more preferred embodiments, the material will
be
resorbed within nine months, six months, three months, and ideally one month.
Furthermore, particularly preferred materials are characterized in that they
can be fully
resorbed in the stated time periods. For the purpose of this disclosure,
"weakly"
resorbable means that less than 80% of the starting material is resorbed after
one year.
"Effective Amount"-- An effective amount of a biologically active agent is an
amount sufficient to elicit a desired biological response.
"Hardening"-- "Hardening" refers to the process by which the hydrated
precursor
is transformed into a hardened PCA material. The PCA material is considered to
be
"hardened" when it is a substantially non-formable solid. Such a hardened PCA
material
has minimal compressibility and tends to undergo plastic as opposed to elastic
deformation.
"Hydrated precursor"-- The term "hydrated precursor", as used herein, refers
to the
paste or putty formed by hydration of the dry PCA precursors in the presence
of a limited
amount of aqueous solution (i.e., less than approximately 1 mL aqueous
solution/1 g
precursor powder). The hydrated precursor may comprise both reactants and
products, in
various combinations, depending on the extent to which the conversion has
progressed.
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Both the "injectable" and "formable" PCA precursor pastes described herein are
hydrated
precursors. Preferred "injectable" hydrated precursors have a consistency
appropriate for
delivery through an 18 gauge needle.
"Poorly crystalline apatitic calcium phosphate", "PCA calcium phosphate" and
"PCA material", as those terms are used herein, describe a synthetic poorly
crystalline
apatitic calcium phosphate. The PCA material is not necessarily restricted to
a single
calcium phosphate phase provided it has the characteristic XRD and FTIR
pattern. A
PCA calcium phosphate has substantially the same X-ray diffraction spectrum as
bone.
The spectrum is generally characterized by only two broad peaks in the region
of 20-35
with one centered at 26 and the other centered at 32 . It is further
characterized by
FTIR peaks at 563 cm', 1034 cm', 1638 cm-' and 3432 cm-' ( 2 cm-'). Sharp
shoulders are observed at 603 cm' and 875 cm', with a doublet having maxima at
1422
cm' and 1457 cm-'.
"Promoter" -- The term "promoter" , as used herein, describes a material or
treatment that promotes hardening of a hydrated precursor and may enhance the
ACP to
PCA calcium phosphate conversion. Some promoters participate in the conversion
and
are incorporated into the product PCA material; others, known as "passive"
promoters,
do not participate.
"Reactive" -- "Reactive" is used herein to refer to the ability of an
amorphous
calcium phosphate when mixed with liquid to form a hydrated precursor to
undergo
conversion to the PCA material of the present invention in the presence of a
promoter in
association with hardening of the precursor materials. Preferred ACPs are
characterized
by an ability to convert completely, an ability to convert quickly with
hardening, an
ability to undergo conversion with otherwise inert compounds and/or an ability
to convert
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into a substantially homogeneous PCA material. Where the ACP is reacted with a
second
calcium phosphate, the "conversion" can encompass conversion of both the ACP
and the
second calcium phosphate. The degree of hardening and the kinetics of the
hardening
process are also important elements of reactivity. Some ACPs are more reactive
than
others. An ACP is considered "highly reactive" if it undergoes conversion and
hardening
to a PCA material in the presence of a weak promoter, such as dicalcium
phosphate
dihydrate ("DCPD") with a grain distribution containing a significant fraction
of grain
sizes greater than 100 gm. Preferred highly reactive ACPs produce a hardened
PCA
material in the presence of weakly promoting DCPD and water at 37 C in less
than twelve
hours, with hardening being substantially complete in about one to five hours,
and ideally
10-30 minutes.
Summary of the Invention
Various embodiments of this invention provide a vehicle for delivering a
biologically active agent, comprising: an amorphous calcium phosphate (ACP),
an acidic
calcium phosphate and an aqueous solution in an amount to provide a paste of
formable or
injectable consistency; and a biologically active agent contained in or on the
paste;
wherein the paste hardens in an endothermic reaction to a poorly crystalline
apatitic (PCA)
calcium phosphate.
Various embodiments of this invention provide a method of producing a vehicle
for delivering a biologically active agent, the method comprising the steps
of: mixing in
any order, an amorphous calcium phosphate (ACP), an acidic calcium phosphate,
an
aqueous solution in an amount to form a paste of formable or injectable
consistency; and
introducing a biologically active agent to the paste, wherein the paste
hardens in an
endothermic reaction to a poorly crystalline apatitic (PCA) calcium phosphate.
Various embodiments of this invention provide a method of producing a vehicle
for delivering a biologically active agent, the method comprising the steps
of: mixing in
any order, an amorphous calcium phosphate (ACP), a biologically active agent,
an acidic
calcium phosphate, and an aqueous solution in an amount to form a paste of
formable or
injectable consistency; and allowing the paste to harden in an endothermic
reaction to a
poorly crystalline apatitic (PCA) calcium phosphate.
Various embodiments of this invention provide a method of producing a vehicle
for delivering a biologically active agent, the method comprising the steps
of: mixing in
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any order, an amorphous calcium phosphate (ACP), an acidic calcium phosphate,
and an
aqueous solution in an amount to form a paste of formable or injectable
consistency;
allowing the paste to harden in an endothermic reaction to a poorly
crystalline apatitic
(PCA) calcium phosphate; and introducing a biologically active agent to the
hardened
PCA calcium phosphate.
Various embodiments of this invention provide use of an injectable or formable
paste comprising a mixture of an amorphous calcium phosphate (ACP), an acidic
calcium
phosphate, a biologically active agent, and an aqueous solution in an amount
to provide a
formable or injectable consistency in the manufacture of a medicament for
delivering a
biologically active agent, wherein, upon application of said paste to a site
requiring
delivery of the biologically active agent, said paste hardens in an
endothermic reaction to a
poorly crystalline apatitic (PCA) calcium phosphate.
Various embodiments of this invention provide a vehicle for delivering a
biologically active agent comprising: a calcium phosphate source comprising:
at least
about 50 wt % amorphous calcium phosphate (ACP) and an acidic calcium
phosphate; and
an aqueous solution in an amount to provide a paste of formable or injectable
consistency
with the calcium phosphate source, the paste being capable of hardening in
association
with an endothermic reaction; and a biologically active agent contained in or
on the paste.
Various embodiments of this invention provide a vehicle for delivering a
biologically active agent comprising: a calcium phosphate source consisting
essentially of
an amorphous calcium phosphate (ACP) and an acidic calcium phosphate; an
aqueous
solution in an amount to provide a paste of formable or injectable consistency
with the
calcium phosphate source, the paste being capable of hardening in association
with an
endothermic reaction; and a biologically active agent contained in or on the
paste.
Various embodiments of this invention provide a bioresorbable implant
composition comprising: an amorphous calcium phosphate (ACP), an acidic
calcium
phosphate and an aqueous solution in an amount to provide a paste of formable
or
injectable consistency; a first agent that directly or indirectly stimulates
osteoclast activity;
and a second agent that is biologically active, wherein the first and second
agents are
different; wherein the first and second agents are contained in or on the
paste, and wherein
the paste hardens in an endothermic reaction to a poorly crystalline apatitic
(PCA) calcium
phosphate.
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Various embodiments of this invention provide use of an injectable or formable
paste comprising an amorphous calcium phosphate (ACP), an acidic calcium
phosphate, a
biologically active agent, and an aqueous solution in an amount to provide a
formable or
injectable consistency in the manufacture of a medicament for growing bone in
vivo,
wherein, upon implantation to a site requiring bone growth, said paste hardens
in an
endothermic reaction to a poorly crystalline apatitic (PCA) calcium phosphate.
The present invention provides a synthetic, poorly crystalline apatitic
calcium
phosphate material that has excellent biocompatibility, resorbability, and
processability
characteristics and is useful in drug delivery and cell seeding (in vivo and
in vitro)
applications.
The synthetic PCA material utilized in the present invention is compatible
with
cells and with a wide array of biologically active agents. The material can be
employed to
deliver agents or cells to any of a variety of sites in the body, or can be
used in vitro. The
material is characterized by a distinctive X-ray diffraction pattern that
reveals its poor
crystallinity. Preferably, the material has a calcium to phosphate ratio in
the range of
about 1.1 to 1.9. More preferably, this ratio is in the range of about 1.3 to
1.5.
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The PCA material utilized in the present invention is strongly bioresorbable.
That
is, when an implant comprising at least 1 g of material is implanted in pellet
form in an
intramuscular or subcutaneous site, at least approximately 80%, preferably 90-
95 %, and
most preferably > 95 %, of the material is resorbed within one year,
preferably within 9
months, 6 months, 3 months, and, ideally 1 month. More preferably, at least
80%,
preferably 90-95%, and most preferably > 95 %, of a 5 g implant is resorbed
within these
time frames. It will be appreciated that the conformation of the material
(e.g., in a
sphere as compared with a rod or other shape) may affect is resorption rate.
Furthermore, the resorption rate of the delivery vehicle can be varied through
its manner
of preparation.
In preferred embodiments of the present invention, the synthetic PCA material
is
formed in a reaction in which at least one amorphous calcium phosphate (ACP)
precursor
is exposed to a promoter. In particularly preferred embodiments, the promoter
comprises
a second calcium phosphate material. The reaction conditions employed to
produce the
PCA material utilized in the present invention are mild, so that biological
agents or cells
can be incorporated into the material during the formation reaction, if
desired.
Alternatively, the agents may be incorporated after the delivery vehicle is
made. The
delivery vehicle material may be formed into any of a variety of useful
delivery shapes,
either before or after the introduction of biologically active agent or cell,
and may be
delivered to the site by, for example, injection or surgical implantation. The
material
may be introduced into a site in a wet, non-hardened state (i.e., as a
hydrated precursor)
and allowed to harden in situ. The vehicle may alternately be hardened in
vitro at an
elevated temperature, generally at or above 37 C, and thereafter surgically
implanted into
a subject (animal or human).
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The PCA material of the present invention may be fabricated in vitro either in
the
presence or absence of the biologically active agent or cell. Alternatively
the biologically
active agent or cell may be added post-hardening by exposing the pre-formed
vehicle to
the agent.
The present invention therefore provides vehicles for delivering biologically
active
agents, which vehicles comprise a PCA calcium phosphate and a biologically
active agent.
The inventive vehicles optionally comprise, for example, other bioresorbable
materials,
erosion rate modifiers, cells, or other factors that modify one or more
characteristics of
the vehicle (such as its strength, adherence, injectability, frictional
characteristics, etc.).
One advantage of the delivery system of the present invention is that it
allows a high local
concentration of drug to be achieved, which is particularly useful with drugs
that have
toxic side effects and also with labile drugs.
The invention also provides methods of preparing delivery vehicles, of
altering
delivery vehicle characteristics, and of delivering biologically active agents
to a site.
Preferred delivery sites include both in vitro and in vivo sites. The delivery
vehicles of
the invention are suitable for delivery into human or animal sites. Preferred
in vivo sites
include bony sites, intramuscular sites, interperitoneal sites, subcutaneous
sites, central
nervous system sites, and occular sites.
The present invention additionally provides therapeutic, structural, or
cosmetic
implants comprising the inventive PCA material and at least one cell.
Preferably, the at
least one cell is a bone-forming or bone-degrading cell. Particularly useful
cell types
include chondrocytes, osteocytes, osteoblasts, osteociasts, mesenchymal stem
cells,
fibroblasts, muscle cells, hepatocytes, parenchymal cells, cells of intestinal
origin, nerve
cells, and skin cells, and may be provided as primary tissue explants,
preparations of
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primary tissue explants, isolated cells, cell lines, transformed cell lines,
and host cells.
The implants may also comprise additional components such as biologically
active agents
or factors that alter the characteristics (such as resorbability, strength,
adherence,
injectability, frictional characteristics, etc.).
The invention also provides methods of preparing such implants; methods of
growing bone or cartilage in vivo or in vitro, at natural sites or ectopic
sites; methods of
osseous augmentation; and methods of diagnosing disease states by assaying
tissue-
forming potential of cells isolated from a host. The invention also provides
in vitro cell
culture systems and cell encapsulation matrices.
Description of the Drawings
Figure 1 is a high-resolution transmission electron micrograph of the reactive
amorphous calcium phosphate illustrating the nanometer-sized grains in
clusters with
relatively unclear boundaries and partially immersed in shapeless form
(arrows);
Figure 2 is an energy-dispersive electron microprobe spectrum of the reactive
amorphous calcium phosphate of the present invention after the vacuum heating
procedure
which yielded Ca/P to be 1.58;
Figure 3 is a solubility curve of a poorly crystalline apatitic calcium
phosphate
product derived from amorphous calcium phosphate of the present invention, as
compared
with a crystalline hydroxyapatite. Note the relative higher solubility of the
material of the
present invention versus a more crystalline form of hydroxyapatite, as
measured by the
amount of calcium ions released into solution at 37 C;
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Figure 4 are X-ray diffraction patterns of (a) reactive amorphous calcium
phosphate; and (b) dicalcium diphosphate used in a reaction to form a bone
substitute
material of the invention;
Figure 5a-d are X-ray diffraction patterns tracking the progress of the
reaction of a
mixture of reactive amorphous calcium phosphate and dicalcium diphosphate to
form a
PCA material of the present invention;
Figure 6 is infrared spectra of (a) dicalcium phosphate dihydrate, (b) the
activated
ACP of the invention, and (c) the PCA material of the present invention;
Figure 7 is an X-ray diffraction pattern of naturally occurring bone.
Figure 8 is a bar graph displaying particle size distribution for various
formulations described in Example 5.
Figure 9 depicts use of the PCA material of the present invention in a variety
of
bony sites.
Figure 10 presents photomicrographs of tibial defects either untreated (l0a)
or
treated (lOb) with the PCA material of the present invention. In Figure 10a,
the small
arrows indicate one edge of the defect; the large arrowhead is at the yet
unbridged defect.
In Figure lOb, large arrowheads denote one edge of the defect. In both
Figures,
magnification is 4x, bone is decalcified, and slides are treated with
hematoxylin and
eosin.
Figure 11 is a photomicrograph of canine trabecular bone grown into a defect 8
weeks after surgery treated with the drug delivery vehicle of the present
invention.
(Magnification lOx; decalcified; hematoxylin and eosin).
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Figure 12 is a photomicrograph of a canine cortical bone defect 4 weeks after
surgery that was treated with the drug delivery vehicle of the present
invention.
(Magnification 4x; undecalcified, Light Green Basic Fuchsin).
Figure 13 presents photomicrographs of untreated (Figure 13a) and treated
(Figure
13b) rabbit tibia defects 4 weeks after surgery (Magnification 4x;
decalcified; Masson's
Trichrome) .
Figure 14 is a photomicrograph of a region external to a bone site in which
cartilage formation has occurred (hematoxylin and eosin).
Figure 15 is an X-ray diffraction pattern of PCA calcium phosphate prepared as
described in Example 1-2;
Figure 16 is and X-ray diffraction pattern of PCA calcium phosphate prepared
as
described in Example 1-4;
Figure 17 is an X-ray diffraction patterns of PCA calcium phosphate prepared
from A1Z03 passive promoter, in which Al P3 peaks are indicated by lines;
Figure 18 shows XRT analysis of material retrieved from rabitts.
Figure 19 shows FTIR analysis of material retrieved from rabbits.
Figure 20 shows results for new bone formation and PCA material resorption.
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Description of Preferred Embodiments
The PCA Material
The PCA material of the present invention is described in United States
Patents
5,676,976 and 6,214,638, and in WO 96/36562. The material is also described in
United
States Patents 5,980,482, 6,117,456, and 6,827,742. In light of the breadth of
disclosures
in each of these related applications, the details of the inventive PCA
materials will not be
belabored here. A summary of its characteristics will suffice.
The PCA material employed in the present invention is characterized by its
biocompatibility, its biological resorbability and its minimal crystallinity.
The material
may be highly porous and rapidly resorbable or of decreased porosity and
slowly
resorbable. Its crystalline character is substantially the same as natural
bone, and lacks
the higher degree of crystalliniry seen in the bone substitute materials known
to the art.
The inventive PCA material also is bioconipatible and not detrimental to the
host.
The PCA material of the present invention may be implanted in a patient in a
paste
or putty form (i.e., as a hydrated precursor). Since the inventive reaction
that produces
the hardened PCA material can be initiated outside the body, and proceeds
slowly at room
temperature, the possibility that the material will "set up" prior to
application to the
surgical site and become unusable is minimized. The reaction accelerates
significantly at
body temperature and the material hardens in place. This feature is
particularly useful in
the surgical setting, where custom fitting of the device to the implant
location is typically
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required. For example, in some preferred embodiments of the invention, an
antibiotic
and/or regenerative factor is delivered to a fracture site. In such
embodiments, the
inventive paste containing the therapeutic agent will be applied to and used
to fill a
fracture site, as well as to deliver the desired agent.
Alternatively, the inventive PCA material may be pre-hardened outside the
body,
loaded with the desired biological agent or cell(s), and implanted at a later
time. This
approach is useful in those situations where custom shapes are not essential,
and where
production of large numbers of implants is desired.
Generally, the formation reaction of the present invention is completed after
application to the surgical site. The material typically hardens in less than
five hours, and
substantially hardens in about one to five hours, under physiological
conditions.
Preferably, the material is substantially hardened within about 10-30 minutes.
The
consistency and formability of the PCA material, as well as the speed of the
formation
reaction, may be varied according to the therapeutic need by modifying a few
simple
parameters.
The resorbability of the PCA material employed in the instant invention is
attributable to the combination of its porosity, its chemical composition, and
its
crystallinity. Apatites have reduced crystalline characters and display
somewhat increased
solubility in aqueous systems when compared with more crystalline species. The
low
crystallinity of the inventive PCA material, and/or the presence of stable
amorphous
domains within it, is believed to promote its resorbability in biological
systems.
The resorbability of the PCA material of the present invention can be modified
by
altering its density and/or porosity. Porosity facilitates both the diffusion
of substances to
and from the interior of the material and, in certain applications, the
penetration of cells
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and cell processes into the material matrix. Drug delivery materials of lower
porosity
tend to resorb more slowly in vivo than do those of higher porosity. In one
embodiment
of the invention, porosity is increased through the use of a dry mixture of
controlled
particle size reactants; in other embodiments, chemical or physical etching
and leaching
techniques are employed.
Thus; different embodiments of the present invention provide PCA materials
with
different resorption rates. Selection of reactants, porosity, final
crystallinity, and amounts
and types of crystallization inhibitors employed yields different embodiments
of the PCA
material of the present invention, so that, in different embodiments, 1 g of
material is
resorbed (i.e., at least 80%, preferably 90-95%, and most preferably >95%,
resorbed)
within any desired time period from 2 weeks to 1, 3, 6, or 9 months, to 1
year.
In a preferred embodiment of the present invention, the reaction that produces
the
PCA material is initiated by adding physiological saline to a mixture of two
dry
components so that a thick paste forms that hardens in about a half an hour.
Other
aqueous agents, such as serum, tissue culture medium, or another buffered
solution or
distilled water, may be used in place of saline. Most often, the resulting
resorbable PCA
material will be "calcium deficient", with a calcium to phosphate ratio of
less than 1.5 as
compared to the ideal stoichiometric value of approximately 1.67 for
hydroxyapatite.
The invention provides a test for identifying suitable PCA materials and
reactive
precursors. Specifically, precursors are combined, are hydrated with a limited
amount of
water (so that a paste or putty is formed), and are allowed to harden into a
PCA material.
Desirable precursors are capable of hardening in a moist environment, at or
around body
temperature. The hardened product is then placed intramuscularly or
subcutaneously in a
test animal. Desirable materials are those that, when implanted as an at least
1 g pellet
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are at least 80%, preferably 90-95 %, and most preferably > 95 %, resorbed
within 1 year
(or less). Preferably, the material can be fully resorbed. Generally, it is
easier to test
resorption of gram quantities of material in subcutaneous sites.
The PCA material of the present invention is formed in a reaction that employs
at
least one amorphous calcium phosphate (ACP) precursor, preferably an activated
ACP
(see, for example, Examples 1-4). In some instances, the reaction may employ
only one
precursor ACP, which is converted in a controlled fashion in part or whole to
the PCA
material of the invention. Alternatively, the reaction may employ a promoter
that
comprises oine or more additional precursors (preferably one or more calcium
and/or a
phosphate sources), that combine with the ACP to yield the PCA material of the
invention. Also, a non-participating promoter may be employed to facilitate
conversion
of the activated ACP to the inventive PCA material. In any event, reactions
that can be
initiated outside of the body, that can be carried on in a paste-like
configuration, and that
significantly accelerate at 37 C leading to a hardened calcium phosphate
product are
greatly preferred.
The conversion of ACP to a PCA material is promoted in the presence of water.
Generally, the ACP is provided as a powder is combined with any other
reactants (e.g. a
second calcium phosphate), and is exposed to a limited amount of water, so
that a paste
or putty is formed. The hydrated precursor then hardens, and the hardening is
associated
with formation of the PCA material. It is an aim of this invention to provide
methods
which promote the conversion of ACP to a PCA material in a controlled fashion,
producing a hydrated precursor paste or putty that hardens predictably and has
utility in
dental, orthopedic, drug delivery, cell therapy, and/or other applications.
The promoters
used to accomplish this conversion may themselves be converted to PCA
material, or may
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participate in other chemical or physical reactions. Some preferred promoters
may also
remain unchanged during the conversion, providing a catalytic or nucleator
function.
Particularly suitable in this regard are substances that provide reactive
surfaces that
weakly promote crystallization to produce PCA calcium phosphate.
ACP precursors only: When amorphous calcium phosphate is used as the sole
precursor to produce a resorbable PCA material, it is important to control the
natural
tendency of the ACP to convert to highly crystalline hydroxyapatite. On the
other hand,
the time course of conversion should be fast enough to have surgical utility.
One
approach is to combine a precursor ACP containing an inhibitor of crystal
formation
(e.g., the ACP of Example 1) with an ACP that does not contain an inhibitor of
crystal
formation (e.g., a promoter). The reactants may be mixed in a dry state, with
the
appropriate particulate size and an excess of the inhibitor-containing ACP.
The reactants
can then be exposed to crystal-forming conditions such as the addition of
water, followed
by an elevation in temperature (e.g., as occurs following introduction into
the body), to
convert the reactants to the PCA material of the invention. Other methods of
controlled
conversion involve the use of catalysts.
ACP precursor plus additional calcium phosphate sources: ACP may be reacted
with a second calcium source (including a second ACP) using any reaction-
promoting
technique. In preferred embodiments, the second calcium source is itself a
promoter.
The reaction being promoted is the conversion of an amorphous calcium
phosphate into a
hardened nanocrystalline or poorly crystalline apatitic calcium phosphate.
Such reactions
include acid/base, displacement, substitution, and hydrolysis reactions as
well as purely
physical and mechanical reactions (e.g., grinding, mixing). Catalytic
conversion, such as
surface-catalyzed conversion of ACP to a PCA material, may also be employed.
Under
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any reaction scheme, it is important that the ACP retains significant
amorphous character
throughout the reaction. Specifically, the overall crystallinity within the
starting ACP
should not exceed that desired in the end product. Thus, certain reaction
schemes may
require stabilization of the amorphous nature of the ACP throughout the
reaction period.
Examples of inhibitors of crystal formation that are known to the art and are
useful for
such stabilization include carbonate, pyrophosphate and magnesium.
In some preferred embodiments, the ACP component is activated under heat in
order to facilitate the conversion being promoted by the second calcium
containing
reactant or other promoter. Examples of suitable such second reactant
promoters include
DCPD, other crystalline or poorly crystalline calcium phosphates, calcium
sources,
phosphate sources, or a second ACP. Other methods of promoting conversion,
such as
catalysis or the use of ionic solvents or promoters of nucleation, may also be
employed to
promote reaction between substituents. The second calcium phosphate reactant
may be of
any crystalline structure and should be chosen so as to be reactive with the
first ACP
either directly or through the use of reaction enhancing vehicles such as
ionic solvents or
catalysts. Appropriate reaction conditions will be determined by demonstration
of rapid
hardening at 37 C after the reactants are mixed and water is added.
The delivery vehicle formation reaction may also be designed to produce an end
product that is porous. In one embodiment, the use of a dry mixture of
controlled
particle size reactants leads to a porous material. Other methods of promoting
porosity,
such as chemical or physical etching and leaching, may be employed.
The present invention provides a novel process for activating a standard
amorphous calcium phosphate precipitate into highly reactive amorphous solids.
The
amorphous solids can be used in the reactions described above to form a poorly-
or
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nanocrystalline synthetic apatitic calcium phosphate that provides
bioactivity,
bioresorbability and structural integrity. The novel amorphous material can be
reacted
with other calcium phosphates at or below 37 C to form a bone-like material
consisting
of poorly crystalline apatitic calcium phosphate.
Prior art acid-base reactions of conventional crystalline calcium phosphates
produce poorly reacted solids, having reaction products that are too
crystalline to be
sufficiently resorbable in living tissues. The reactions from the prior art
are generally
incomplete and the reaction products are inhomogeneous. In contrast, the
amorphous
calcium phosphate of the present invention reacts quickly and completely with
a wide
variety of calcium phosphates and other calcium- or phosphorus-bearing
materials to
provide a homogeneous product.
The source of the enhanced reactivity of the ACP of the present invention is
not
completely understood; however, it is believed to be associated with the
amorphicity (lack
of crystallinity) and, in some embodiments, ion pair site vacancies in the
material, as
created by the process of the present invention. The vacancies may provide
reactive sites
for subsequent reaction. These observations will be discussed more fully,
below.
The method of the present invention permits initial formation of amorphous
calcium phosphate particles of less than 1000 A, preferably 200-500 A, and
most
preferably 300 A, the further growth of which is curtailed by rapid
precipitation of the
product from solution. During reaction of calcium and phosphate ion sources to
form an
amorphous calcium phosphate, a third ion is introduced in the solution so that
this third
ion is incorporated in the amorphous precipitate structure instead of
trivalent P043'
group(s). Because some P043- is replaced by the third ion, the overall P043-
decreases,
thus increasing the Ca/P ratio of the amorphous precipitate (as compared to
standard
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amorphous calcium phosphate) and modifying the valence or charge state of the
calcium
phosphate. The amorphous solids then may be rapidly freeze-dried to preserve
the
chemical and physical properties of the material. The amorphous solids then
may be
treated under specific conditions selected to promote removal of at least some
of the third
ion. Where the third ion is carbonate, specific temperature and pressure
conditions lead
to the reduction of total carbon, presumably as gaseous carbon dioxide from
the
amorphous solid, while maintaining the product amorphicity.
The resultant material is an amorphous solid with a higher Ca/P ratio than is
typically found in amorphous calcium phosphates, where the ratio generally
reported in
the past is 1.50. Further, removing carbon from the material results in a
vacancies in the
interstitial structure within the amorphous solids, rendering it a highly
reactive solid.
There may be several possible vacancies sources. The material possesses a
porosity
which promotes reactivity by various means, such as increased surface area.
The
material may also undergo a change in the stoichiometry balance upon removal
of the
third ion. This stoichiometry change may result a charge imbalance which is
responsible
for the increased reactivity of the amorphous calcium phosphate.
It is desirable to maintain substantial amorphous character within the
material
throughout the entire process. If crystallinity in its entirety (single
crystalline regions), or
even in local domains (microcrystalline regions), is introduced to excess
during the
process or in the final product, the solid has been found to be less reactive.
The resultant
highly reactive calcium phosphate is amorphous in nature and has a calcium to
phosphorous ratio in the range of 1.55 to 1.65. In a preferred embodiment, the
amorphous calcium phosphate has a Ca/P ratio of about 1.58.
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The amorphous state of the amorphous calcium phosphate is induced by
controlling the rate and duration of the precipitation process. The amorphous
calcium
phosphate of the present invention is precipitated from solution under
conditions where
initial precipitation is rapid. Rapid precipitation results in the formation
of many
extremely small calcium phosphate nuclei. Additionally, rapid crystal or grain
growth
leads to the production of more defects within each grain, thereby also
increasing
solubility. At the extreme end of the spectrum, crystal or grain growth is so
rapid and
defect density is so significant that an amorphous calcium phosphate results.
Amorphous
calcium phosphate is gel-like and includes solid solutions with variable
compositions.
These gels have no long range structure, but are homogeneous when measured on
an
Angstrom scale. Under physiological conditions, these amorphous compounds have
high
solubilities, high formation rates and high rates of conversion to poorly
crystalline apatitic
calcium phosphate.
The amorphous calcium phosphate solids acquired by this method retain their
amorphous nature sufficiently long enough to be introduced into the final
reaction as
substantially amorphous solids. They can also be mixed and reacted with other
solids or
solutions containing phosphates, to obtain solids containing a homogeneous
distribution of
nanometer-sized crystals. Further, in preferred embodiments, because the
amorphous
calcium phosphate reacts completely with the other solids, the Ca/P of the
resultant solid
will constitute the total calcium and phosphorous from such reaction, i.e.,
there will be an
essentially complete reaction. When a proper molar concentration of phosphate
from the
solution or solids is reacted with the novel amorphous calcium phosphate
material, a
poorly crystalline apatitic calcium phosphate material (Ca/P 1.1-1.9) is
obtained. Thus,
the present invention permits one to design and modify the chemical
composition of the
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resultant product, thereby providing a further mode of controlling bioactivity
of the fmal
product used as a delivery vehicle or cell scaffold.
In one embodiment of the present invention, a solution is prepared that
contains
calcium and phosphate ions and a third ion in a concentration, at a pH, and at
a
temperature that will promote the rapid nucleation and precipitation of
calcium phosphate.
When precipitation is sufficiently rapid, an amorphous gel-like calcium
phosphate is
formed. Because the thermodynamically favored crystalline form of
hydroxyapatite is
enhanced by reducing the rate of reaction, certain processing steps of
increasing the rate
of reaction may be taken to ensure that an amorphous compound is obtained. The
following factors, among others, are to be considered when designing a
solution for the
rapid precipitation of the amorphous calcium phosphate of the present
invention.
Preferred conditions: Rapid mixture of calcium and phosphate sources to
increase
the rate of reaction. The rate of reaction is increased to favor non-stable
phases as a
product. Allowing more reaction time for each of the ions to juxtapose
correctly to form
a solid will result in a more thermodynamically favorable crystalline and
stable structure.
Preferred calcium and phosphate sources: The use of highly concentrated or
near
supersaturation solutions ensures that a more rapid reaction will occur.
Preferred temperature: Although the reaction can be carried out at room
temperature, temperatures of near boiling point to increase the concentration
of one
reactant is a possible means of increasing the rate of reaction.
In one embodiment calcium ions, phosphate ions and carbonate ions are mixed
together rapidly in an aqueous solution to obtain a carbonate containing
amorphous
calcium phosphate solid. The relative concentrations of the ions are selected
to give a
precipitate having the desired Ca/P ratio. The carbonate ion substitutes for a
phosphate
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ion in the amorphous calcium phosphate. The carbonated amorphous calcium
phosphate
may be obtained by precipitation from an aqueous carbonate solution. Suitable
aqueous
carbonate solutions include, by way of example only, bicarbonate solution,
sodium
carbonate solution, potassium carbonate solution. It is further contemplated
as within the
scope of the invention to use non-aqueous solutions.
Use of a carbonated material is desirable because it permits manipulation of
the
Ca/P ratio by substitution of P043- by C032- . Additionally, the presence of
CO3 2- is
known to retard the development of crystallinity in amorphous calcium
phosphate. Is
recognized, however, that other ions or a mixture of ions may be suitable in
place of or
in addition to carbonate ion in modifying the Ca/P ratio and in introduction
of reactive
site vacancies into the amorphous calcium phosphate, such as by way of example
only,
nitrate, nitrite, acetate, Mg+2 and P2074- ions.
The amorphous calcium phosphate precipitate may be collected and filtered
prior
to activation. It is preferred to perform this step in a cold room or at sub-
ambient
temperatures so as to preserve the amorphous state of the precipitate
collected. Collection
may typically be carried out by any conventional means, including, but in no
way limited
to, gravity filtration, vacuum filtration or centrifugation. The collected
precipitate is
gelatinous and is washed more than once with distilled water.
The washed precipitate is then dried under any conditions that maintain the
amorphous character of the material. Lyophilization is a suitable, but not
exclusive,
technique. The precipitate is frozen and, while being kept frozen, is dried to
remove the
bulk of the entrained liquid. This procedure may be accomplished by placing
the frozen
precipitate into a vacuum chamber for a given period of time. Freeze-drying
typically
occurs at liquid nitrogen temperatures for a time in the range of 12-78 hrs,
preferably
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about 24 hours, and under a vacuum in the range of 10-'-10', preferably 10',
torr. A
preferred method includes lyophilization because the cryogenic temperatures
typically
used in lyophilization inhibit further crystallization of the material. As a
result, the
amorphous calcium phosphate obtained thereby is an extremely fine free flowing
powder.
The dried ACP may then be activated. In a preferred embodiment, where
carbonate is present in the ACP, the ACP powder is heated to drive off
remaining free
water and water of hydration and to remove carbon, presumably through the
decomposition of C032- into CO2 and oxygen. The heating step is carried out at
a
temperature of less than 500-600 C but more than 425 C, so as to prevent
conversion of
the amorphous calcium phosphate into crystalline hydroxyapatite. Heating is
preferably
carried out at a temperature in the range of 450-460 C, preferably for 1/2
hour to 6
hours.
Low crystallinity and site vacancies (porosity and/or stoichiometric changes)
may
account for the observed higher reactivity of the activated amorphous calcium
phosphate
of the present invention. This is exemplified by the following observations. A
carbonate-
containing amorphous calcium phosphate which has been heated to 525 C is
observed to
have an increase in formation of crystalline hydroxyapatite and to have a
corresponding
decrease in reactivity. Amorphous calcium phosphate that is heated to only 400
C
retains its amorphous characteristic, but exhibits a decreased reactivity.
Presumably this
decrease in reactivity is related to the higher carbonate levels (and fewer
site vacancies)
observed by IR in samples treated at this lower temperature. These findings
suggest that
both amorphicity and decreased carbon content (vacant reactive sites) are a
factor in
reactivity. This is not intended to be in any way an exclusive basis for
reactivity. Other
bases for the observed reactivity are considered to be within the scope of the
invention.
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The resulting amorphous calcium phosphate powder is a highly reactive
amorphous
calcium phosphate material with a Ca/P ratio of between 1.1-1.9, preferably
about 1.55 to
1.65, and most preferably about 1.58. The powder has been characterized by a
variety of
analytical techniques.
In Figure 1, a high-resolution transmission electron micrograph is shown to
illustrate the morphological characteristics and the angstrom-sized nature of
the preferred
reactive amorphous calcium phosphate of the present invention. Preferred
particle sizes
are less than 1,000 A, preferably in the range of 300-400 A. Note the unclear
boundaries
separating the globule-like clusters, lacking clear edges and surfaces, in
contrast to
crystalline materials.
The amorphous nature of the reactive ACP of the invention is characterized by
an
X-ray pattern that is devoid of sharp peaks at any position of the diffracting
angles that
correspond to known crystalline calcium phosphates (Figure 4a). The Ca/P
measurement
performed using wave length-dispersive X-ray analysis on an electron micro-
probe of the
same material after heat treatment yields Ca/P to be 1.58 (Figure 2).
These characterizations demonstrate that although there is a change in the
local
moiety of certain groups in the amorphous calcium phosphate solids, the
overall
amorphicity is maintained throughout the process.
In another preferred embodiment, the highly reactive amorphous calcium
phosphate is reacted with a second calcium phosphate to obtain a PCA material.
As
discussed above, crystalline hydroxyapatite is the thermodynamically preferred
reaction
product, and is usually described as not resorbable under physiological
conditions. The
use of an amorphous calcium phosphate, which can convert quickly and
completely to
produce an apatitic compound without significant crystallization, provides a
novel route to
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a poorly-crystalline apatitic calcium phosphate that is resorbable under
physiological
conditions.
The amorphous calcium phosphate powder of the present invention may be mixed
with a promoter and thereby convert to form a PCA material. This reaction may
occur at
rooin temperature upon mixing of the powder with any of a variety of both
acidic and
basic calcium phosphates in the presence of a limited amount of a fluid such
as, but not
limited to, water, saline, buffer solution, serum or tissue culture medium.
Depending
upon the amount of fluid added, the mixture of amorphous calcium phosphate of
the
present invention and a second calcium phosphate results in a highly formable
and/or
highly injectable paste with varying degrees of paste consistency.
The method of preparation of the promoter and/or the ACP will affect the ease
by
which the hydrated precursor is converted into the PCA material. As noted
above, the
method of mixing the powdered reactants prior to addition of liquid affects
the reactivity
of the system. Thus, hand mixing using a mortar and pestle does not result in
as reactive
a system as a prolonged machine grinding of the reactant powders. Therefore
when
comparing promoters, it is important to use standardized preparation
conditions.
It is hypothesized that the conversion of ACP to the reactive PCA calcium
phosphate is a surface catalyzed phenomenon. If so, it may be desirable to
produce a
particular promoter with a reproducible surface area. Specific surface area of
the ACP
and promoter powders can be controlled to control the reaction conditions and
final PCA
material properties. Thus, to control reaction reproducibility it is
advantageous to provide
a promoter with a known grain size distribution. Standard sieving techniques
are suitable
for selection of specific grain sizes. Surface area has been shown to be
correlated to the
compressive strength, and possibly the porosity and resorbability, of the PCA
material.
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Many calcium- or phosphate-containing compounds may be used as participating
promoters in the hardening reaction. A calcium phosphate promoter, may be of
any
crystalline structure and should be chosen so as to be reactive with ACP
either directly or
through the use of enhancing promoters. Preferred participating promoters are
those
which tend themselves to undergo conversion to hydroxyapatite through an
intermediate
PCA calcium phosphate phase.
Appropriate calcium phosphates for use as promoters with the ACP described
herein include neutral, basic, and acidic calcium phosphates, preferably
apatitic
phosphates, that provide the appropriate stoichiometry for reaction to obtain
a apatitic
calcium phosphate. In a preferred embodiment, an acidic (pH 5-7) calcium
phosphate is
used. Suitable calcium phosphates include, but are in no way limited to,
calcium
metaphosphate, dicalcium phosphate dihydrate, heptacalcium decaphosphate,
tricalcium
phosphates, calcium pyrophosphate dihydrate, the poorly crystalline apatitic
material of
the invention, calcium pyrophosphate, octacalcium phosphate, tetracalcium
phosphate and
additional ACPs. Other solids that would provide a source of phosphate or
calcium, such
as, by way of example only, CaO, CaCO3, calcium acetate, and H3PO41 may be
mixed to
form a final product to yield a desired Ca/P ratio close to about 1.1-1.9,
preferably about
1.3 to 1.5. It may be desirable to provide the second component in the
amorphous or
poorly crystalline state, as well.
Some calcium phosphate promoters may be prepared as either weak promoters or
strong promoters. For instance, a DCPD sample with a grain size in the range
of 100-
125 m (or distribution B3 in Example 5) reacts only marginally with the
highly reactive
ACP of the invention under certain conditions (see Example 5). DCPD of this
grain size
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may be considered "weakly promoting". Thus, DCPD may be used in this format to
screen for highly reactive ACPs.
In some embodiments of the invention, it is not required that the reaction
employ a
participating second calcium phosphate to produce a PCA material. Rather, it
is within
the scope of the invention.to merely promote hardening and the conversion of
the reactive
ACP into a PCA material by addition of one or more "passive" promoters (also
termed
"non-reactive" or "non-participatory" promoters) that do not participate in
the reaction.
Suitable passive promoters include, but are not limited to, materials or
treatments that
have previously been described as promoting conversion of calcium phosphate
materials
into hydroxyapatite. For example, water, heat, nucleators and catalysts can be
used as
passive promoters. In some embodiments, the catalysts provide surface area,
the
presence of which promotes the hardening and conversion of ACP to poorly
crystalline
apatitic calcium phosphate. For example, A1203, mica, glass and sand, among
other
things, are useful passive promoters. In preferred embodiments, material
promoters are
employed that are insoluble or of low solubility in water, may be prepared in
granular
form in the range of 1-200 m in diameter and are resorbable in vivo. Thus,
polymers
such as poly L-lactic acid (PLLA) and polyglycolic acid (PGA) are particularly
desirable
promoters.
Where a second calcium phosphate is employed as a promoter, it is often
crystalline, as is evidenced by the presence of sharp diffraction peaks
typical to the
calcium phosphate of interest in the X-ray diffraction pattern (Fig 4b). In
contrast, the
reactive ACP is amorphous and shows no identifiable peaks by X-ray diffraction
(Fig 4a).
Despite its higher crystallinity, however, X-ray diffraction suggests that
dicalcium
diphosphate is consumed in the reaction with reactive ACP and the product PCA
material
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is of much reduced crystallinity. Similarly, when stoichiometric HA is
employed as a
second calcium phosphate source, it is also consumed in the reaction and a PCA
material
of reduced crystallinity is produced.
Because at least one of the reactants is amorphous and highly reactive, the
formation reaction of the present invention proceeds at or above room
temperature to
provide a hardened apatitic material having a poorly-crystalline or
microcrystalline
microstructure. In preferred embodiments, the conversion reaction also is
substantially
complete, thereby insuring that all calcium and phosphate of the mixture are
consumed by
the resultant PCA product. This result permits reliable manufacture of
apatitic products
simply by selection of the relative proportions of the starting amorphous and
secondary
calcium phosphates. It is desirable to maintain a calcium to phosphate ratio
of about 1.2-
1.68, preferably less than 1.5, and most preferably about 1.38.
The product apatitic material contains labile environments characteristic of
naturally-occurring bone. In naturally occurring bone, minerals are
characterized by
nanometer-sized structure, providing high surface areas to interact with the
surrounding
tissue environment, resulting in resorption and remodelling of tissues. The
present
invention, with its nanometer-sized crystals as the product, closely mimics
the naturally
occurring bone minerals. Further, properties such as crystallinity and Ca/P
ratios are
closely designed in the present invention to simulate the mineral properties
found in living
tissues of bone.
The PCA produced during the inventive reaction is associated with hardening of
the hydrated precursor material. It should be noted, however, that while
complete
conversion of the ACP precursor is a preferred embodiment, hardening of the
hydrated
precursors may occur prior to complete conversion or even in the absence of
complete
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conversion. Such partially converting, but nonetheless hardening, reactions
are
considered to be within the scope of the invention.
As mentioned above, combination of dry ACP with any other reactants and a
limited amount of aqueous solution produces a hydrated precursor. By selecting
the
appropriate amount of liquid to be added to the reactants, the viscosity of
the may be
adjusted according to need. The hydrated precursor may be prepared either with
an
injectable or a formable consistency. Injectable consistency means as thick as
possible
while still capable of passing through a 16 to 18 gauge needle. Most often,
this will be a
"toothpaste"-like consistency. Formable refers to consistency that allows the
material to
retain its shape. In the extreme case of a formable consistency, the hydrated
precursor
will have the consistency of glazing putty or caulking compounds. The hydrated
precursor also may be prepared with just enough liquid to be both injectable
and
formable. In the paste form, the material has markedly improved flow
characteristics
over prior art compositions. Flow characteristics are toothpaste-like while
prior art
materials generally exhibit a granular or oatmeal-like consistency. The
hydrated
precursor may be prepared before use, up to a period of several hours if held
at room
temperature and if evaporation is minimized. The storage time may be extended
by
maintaining the paste at reduced temperatures in the range of 1-10 C in the
refrigerator
provided steps are taken to minimize evaporative loss.
In some preferred embodiments (e.g., Examples 9-14, below), the reaction is
endothermic and occurs slowly at room temperature, but is accelerated
significantly at
body temperature. This is particularly useful in a surgical situation, since
the paste
formed by mixing reactants with water remains injectable for a considerable
period of
time (up to several hours) while held at or below room temperature. Thus, at
room
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temperature (ca. 22 C) the paste hardens after a time greater than one hour
and remains
formable and/or injectable for longer than 10 minutes, preferably longer than
one hour,
and most preferably longer than three hours. Following injection at the
implant site (ca.
37 C), the paste hardens in less than about an hour, preferably in about 10-
30 minutes.
Comtwsites and Additives
The PCA material of the instant invention may be formed as a composite with
other substances. Composites may be desirable to change any number of physical
parameters of the vehicle including but not limited to strength, resorption
time,
adherence, injectability, frictional characteristics, or therapeutic agent
carrying capacity or
release kinetics. In general, those practiced in the art of composite
fabrication will
understand the methods and concepts important in composite fabrication.
Additional
guidance for the preparation of PCA material composites may be obtained in
United States Patent 6,827,742.
In vitro Imylant Formation
In addition to surgical application in paste form, the inventive implants may
be
pre-formed outside the body, hardened, and implanted in the solid form. Pre-
formed
devices may be hand shaped, molded or machined. Loading of the therapeutic
agent may
be accomplished by addition of the agent directly to the buffer or vehicle
used to prepare
the hydrated precursor. Alternatively, after hardening, the vehicle may be
exposed to the
therapeutic agent using dipping, rolling or spray coat methods.
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Biologically Active Agents
Any biologically useful agent may be delivered from the inventive PCA material
implant. In general, the only requirement is that the substance remain active
in the
presence of the material during fabrication or be capable of being
subsequently activated
or re-activated. Since the inventive paste can be prepared with a large number
of aqueous
vehicles and substituents, those in the art will be familiar with which
specific additives
can be included in order to improve stability of the agent. The stability
and/or
compatibility of a particular agent with the inventive material, as well as
fabrication
strategies, may be tested empirically in vitro. Specifically, the agent may be
incorporated
into the inventive material by one or more of the of the methods described
herein.
Following hardening of the vehicle at 37 C, the substance may be leached from
the
material into an analysis medium such as water or an appropriate buffer and
the
compound collected from the Material by diffusion into the analysis medium.
The
analysis medium may then be analyzed for the presence of active agent. In some
instances, the material will be broken up, pulverized, or otherwise fragmented
prior to
contacting the analysis medium. Other methods of analysis that do not require
agent
diffusion, such as the growth of cells on the material or other physical,
chemical, or
biological assays will be known to practitioners for specific compounds.
Biologically active agents useful in the practice of the present invention
include
any substance having biological activity, including organic molecules,
proteins, peptides,
nucleic acids, nucleoproteins, polysaccharides, glycoproteins, lipoproteins,
and synthetic
and biologically engineered analogs thereof. Also included are chemical agents
that have
biological effects (e.g., antibiotics, dyes, etc.). Proteins can be prepared
by synthetic,
biochemical, or recombinant techniques. Preferably, though not necessarily,
the
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biologically active agent is one that has been deemed safe and effective for
use by an
appropriate governmental agency or body. For example, drugs approved for human
use
in the United States are listed by the Food and Drug Administration (FDA)
under 21
C.F.R. 330.5, 331-361, and 440-460; drugs approved for veterinary use in
the United
States are listed by the FDA under 21 C.F.R. 500-582.
The term "biologically active agent" includes pharmacologically active
substances
that produce a local or systemic effect in animals, plants, or viruses. The
term thus
means any substance intended for use in the diagnosis, cure, mitigation,
treatment or
prevention of disease or in the enhancement of desirable physical or mental
development
and conditions in an animal, plant, or virus. The term "animal" used herein is
taken to
mean mammals, such as primates (including humans), sheep, horses, cattle,
pigs, dogs,
cats, rats, and mice; birds; reptiles; fish; insects; arachnids; protists
(e.g. protozoa); and
prokaryotic bacteria.
Classes of biologically active compounds that can be loaded into the delivery
vehicle of the present invention include, but are not limited to, anti-AIDS
substances,
anti-cancer substances, antibiotics, ACE inhibitors, antigens, adrenergic
antagonists,
antacids, immunosuppressants, anti-viral substances, enzyme inhibitors,
neurotoxins,
opioids, hypnotics, antihistamines, lubricants, tranquilizers, anti-
convulsants, muscle
relaxants and anti-Parkinson substances, anti-spasmodics and muscle
contractants, anti-
diarrheals, anti-emetics, laxatives, diuretics, miotics and anti-cholinergics,
anti-glaucoma
compounds, anti-parasite and/or anti-protozoal compounds, anti-hypertensives,
analgesics,
anti-pyretics, anti-inflammatory agents, anti-histamines, anti-tussive agents,
anti-vertigo,
antinertigic and anti-motion sickness medications, local anesthetics,
ophthalmics,
prostagiandins, anti-depressants, anti-psychotic substances, anti-emetics,
imaging agents,
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specific targeting agents, trophic factors, growth factors,
immunosuppressants,
immunoactivators, anti-mitotics neurotransmitters, proteins, cell response
modifiers,
vaccines, nucleic acids, genes, gene fragments, gene regulatory sequences
(such as
promoters, enhancers, or other regulatory sites), antisense molecules, and
other bioactive
moieties or components of biosynthetic pathways.
A more complete listing of classes of compounds suitable for loading into
delivery
vehicles according to the present invention may be found in the
Pharmazeutische
Wirkstoffe (Von Kleemann et al. (eds), Stuttgart, New York, 1987), or in any
of a variety
of available pharmacology textbooks, such as Lippincott's Illustrated
Pharmacology
Reviews (Harvey et al. (eds), J.B. Lippincott Co., Philadelphia, 1992) or
Examination &
Board Review Pharmacology (Katzing et al., Appleton & Lange, Connecticut,
1993), each
of which is incorporated herein by reference. Examples of particular
biologically active
substances are presented below:
Angiogenic factors are substances that stimulate the growth of vasculature and
include compounds such as veg-f, and some growth factors and mitogens.
Anti-AIDS substances are substances used to treat or prevent Autoimmune
Deficiency Syndrome (AIDS). Examples of such substances include CD4,
3'-azido-3'-deoxythymidine (AZT), 9-(2-hydroxyethoxymethyl) -guanine
acyclovirQ,
phosphonoformic acid, 1-adamantanamine, peptide T, and 2',3' dideoxycytidine.
Anti-cancer substances are substances used to treat or prevent cancer.
Examples
of such substances include anti-metabolites (such as, for example,
methotrexate, fluorouracil, 5-fluorouracil, cytarabine, mercaptopurine, 6-
mercaptopurine,
6-thioguanine), antibiotics (such as, for example, daunorubicin, doxorubicin),
alkylating
agents (such as for example, mechlorethamine, cyclophosphamide, uracil
mustard,
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busulfan, carmustine, lomusline), mitotic spindle poisons (such as, for
example,
vinblastine, vincristine), hormones (such as, for example,
hydroxyprogesterone,
medroxyprogesterone acetate, magistral acetate, diethylstilbestrol,
testosterone propionate,
fluoxymesterone), and other agents (such as, for example, vindesine,
hydroxyurea,
procarbazine, aminoglutethimide, melphalan, chlorambucil, acarbazine (DTIC:
dimethyltriazenomidazole
carboxamide), cytosine arabinoxide).
Antibiotics are art recognized and are substances which inhibit the growth of
or
kill microorganisms. Antibiotics can be produced synthetically or by
microorganisms.
Examples of antibiotics include bactericidal agents, such as aminoglycosides
(e.g.,
gentamicin, tobramycin, netilmicin, streptomycin, amikacin, neomycin),
bacitracin,
corbapenems (e.g., imipenem/cislastatin), cephalosporins, colistin,
methenamine,
monobactams (e.g., aztreonam), penicillins (e.g., penicillin G, penicillin V,
methicillin,
natcillin, oxacillin, cloxacillin, dicloxacillin, ampicillin, amoxicillin,
carbenicillin,
ticarcillin, piperacillin, mezlocillin, aziocillin), polymyxin B, quinolones,
and
vancomycin; and bacteriostatic agents such as chloramphenicol, clindamyan,
macrolides
(e.g., erythromycin, azithromycin, clarithromycin), lincomyan, nitrofurantoin,
sulfonamides, tetracyclines (e. g. , tetracycline, doxycycline, minocycline,
demeclocyline),
and trimethoprim. Also included are metronidazole, fluoroquinolones, and
ritampin.
Antibiotics are sometimes provided in insoluble form, which can be used where
delayed
delivery is desired.
Anti-viral agents are substances capable of destroying or suppressing the
replication of viruses. Examples of anti-viral agents include a-methyl-P-
adamantane
methylamine, 1,-D-ribofuranosyl-1,2,4-triazole-3 carboxamide,
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9-[2-hydroxy-ethoxy]methylguanine, adamantanamine, 5-iodo-2'-deoxyuridine,
trifluorothymidine, interferon, and adenine arabinoside. Particular agents
useful in the
treatment of herpes viruses include acyclovir, vidarabine, idoxuridine, and
ganciclovir.
Enzyme inhibitors are substances which inhibit an enzymatic reaction. Examples
of enzyme inhibitors include edrophonium chloride, N-methylphysostigmine,
neostigmine
bromide, physostigmine sulfate, tacrine HC1, tacrine, 1 -hydroxy maleate,
iodotubercidin,
p-bromotetramisole, 10-(alpha-diethylaminopropionyl)- phenothiazine
hydrochloride,
calmidazolium chloride, hemicholinium-3, 3,5-dinitrocatechol, diacylglycerol
kinase
inhibitor I, diacylglycerol kinase inhibitor II, 3-phenylpropargylamine,
N6-monomethyl-L-arginine acetate, carbidopa, 3-hydroxybenzylhydrazine HCI,
hydralazine HCI, clorgyline HCI, deprenyl HCI,L(-)-, deprenyl HC1,D(+)-,
hydroxylamine HCI, iproniazid phosphate, 6-MeO-tetrahydro-9H-pyrido-indole,
nialamide, pargyline HCI, quinacrine HCI, semicarbazide HCI, tranylcypromine
HCI,
N,N-diethylaminoethyl-2,2-diphenylvalerate hydrochloride, 3-isobutyl-l-
methylxanthne,
papaverine HCI, indomethacind, 2-cyclooctyl-2-hydroxyethylamine hydrochloride,
2,3-dichloro-a-methylbenzylamine (DCMB),
8,9-dichloro-2,3,4,5-tetrahydro-lH-2-benzazepine hydrochloride, p-
aminoglutethimide,
p-aminoglutethimide tartrate,R(+)-, p-aminoglutethimide tartrate,S(-)-, 3-
iodotyrosine,
alpha-methyltyrosine,L-, alpha -methyltyrosine,D L-, acetazolamide,
dichlorphenamide,
6-hydroxy-2-benzothiazolesulfonamide, and allopurinol.
Neurotoxins are substances which have a toxic effect through their action on
the
nervous system, e.g. nerve cells. Neurotoxins include adrenergic neurotoxins,
cholinergic neurotoxins, dopaminergic neurotoxins, calcium channel blockers,
and other
neurotoxins. Examples of adrenergic neurotoxins include
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N-(2-chloroethyl)-N-ethyl-2-bromobenzylamine hydrochloride. Examples of
cholinergic
neurotoxins include acetylethylcholine mustard hydrochloride. Examples of
dopaminergic
neurotoxins include 6-hydroxydopamine HBr, 1-methyl-4-(2-methylphenyl)-1,2,3,6-
tetrahydro-pyridine hydrochloride, 1-methyl-4-phenyl-2,3- dihydropyridinium
perchlorate,
N-methyl-4-phenyl-1,2,5,6- tetrahydropyridine HC1, 1-methyl-4-phenylpyridinium
iodide.
Examples of calcium channel blockers include Sl-conatoxin and verapamil.
Opioids are substances having opiate like effects that are not derived from
opium.
Opioids include opioid agonists and opioid antagonists. Opioid agonists
include codeine
sulfate, fentanyl citrate, hydrocodone bitartrate, loperamide HCI, morphine
sulfate,
noscapine, norcodeine, normorphine, thebaine. Opioid antagonists include
nor-binaltorphimine HCI, buprenorphine, chlornaltrexamine 2HCl,
funaltrexamione HCI,
nalbuphine HCI, nalorphine HCI, naloxone HCI, naloxonazine, naltrexone HCI,
and
naltrindole HCI.
Hypnotics are substances which produce a hypnotic effect. Hypnotics include
pentobarbital sodium, phenobarbital, secobarbital, thiopental and mixtures,
thereof,
heterocyclic hypnotics, dioxopiperidines, glutarimides, diethyl isovaleramide,
a-bromoisovaleryl urea, urethanes and disulfanes.
Antihistamines are substances which competitively inhibit the effects of
histamines.
Examples include pyrilamine, chlorpheniramine, tetrahydrazoline, and the like.
Lubricants are substances that increase the lubricity of the environment into
which
they are delivered. Examples of biologically active lubricants include water
and saline.
Tranquilizers are substances which provide a tranquilizing effect. Examples of
tranquilizers include chloropromazine, promazine, fluphenzaine, reserpine,
deserpidine,
and meprobamate.
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Anti-convulsants are substances which have an effect of preventing, reducing,
or
eliminating convulsions. Examples of such agents include primidone, phenytoin,
vaiproate, Chk and ethosuximide.
Anti-inflammatories are compounds that inhibit inflammation. Different types
of
anti-inflammatory drugs block different chemical mediators. Examples of anti-
inflammatory agents include nonsteroidal anti-inflammatory drugs (NSAIDS),
such as
aspirin, phenylbutazone, indomethacin, sulindac, tolmetin, ibuprofen,
piroxicam,
fenamates, which have anti-inflammatory, analgesic, and antipyretic
activities. Also
included are non-narcotic analgesics such as acetaminophen and phenacetin,
although the
anti-inflammatory activity of these drugs is weaker. Certain slow-acting anti-
inflammatories, such as gold salts, chloroquine, D-Penicillamine, and
methotrexate are
useful in the treatment of arthritis. Gout-specific anti-inflammatories
include colchicine,
allopurinol, probenecid, and sulfinpyrazone.
Muscle relaxants and anti-Parkinson agents are agents which relax muscles or
reduce or eliminate symptoms associated with Parkinson's disease. Examples of
such
agents include mephenesin, methocarbomal, cyclobenzaprine hydrochloride,
trihexylphenidyl hydrochloride, levodopa/carbidopa, and biperiden.
Anti-spasmodics and muscle contractants are substances capable of preventing
or
relieving muscle spasms or contractions. Examples of such agents include
atropine,
scopolamine, oxyphenonium, and papaverine.
Miotics and anti-cholinergics are compounds which cause bronchodilation.
Examples include echothiophate, pilocarpine, physostigmine salicylate,
diisopropylfluorophosphate, epinephrine, neostigmine, carbachol, methacholine,
bethanechol, and the like.
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Anti-glaucoma compounds include betaxalol, pilocarpine, timolol, timolol
salts,
and combinations of timolol, and/or its salts, with pilocarpine.
Anti-parasitic, -protozoal and fungals include ivermectin, pyrimethamine,
trisulfapyrimidine, clindamycin, amphotericin B, nystatin, flucytosine,
ketocanazol,
fluconazole, natamycin, miconazole, metronidazole, diloxanide furoate,
paromomycin,
chlorquine, emetine, dehydroemetine, sodium stibogluconate, (for
leishmaniasis),
melarsoprol (for trypanosomiasis), nifurtimox (for trypanosomiasis), suramin
(for
trypanosomiasis), pentamidone (for trypanosomiasis), and anti-malarial agents
(such as,
for example, primaquine, chloroquine, quinine, mefloquine, pyrimethamine, and
chlorquanide).
Anti-hypertensives are substances capable of counteracting high blood
pressure.
Examples of such substances include alpha-methyldopa and the pivaloyloxyethyl
ester of
alpha-methyldopa.
Analgesics are substances capable of preventing, reducing, or relieving pain
and
Anti pyretics are substances capable of relieving or reducing fever. Examples
of such
substances include aspirin, phenybutazone, idomethacin, sulindac, tolmetic,
ibuprofen,
piroxicam, fenamates, acetaminophen, phenacetin, morphine sulfate, codeine
sulfate,
meperidine, and nalorphine.
Local anesthetics are substances which have an anesthetic effect in a
localized
region. Examples of such anesthetics include procaine, lidocain, tetracaine
and dibucaine.
Ophthalmics include diagnostic agents such as sodium fluorescein, rose bengal,
methacholine, adrenaline, cocaine, and atropine. Ophthalmic surgical additives
include
alpha-chymotrypsin and hyaluronidase.
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Prostaglandins are art recognized and are a class of naturally occurring
chemically
related, long-chain hydroxy fatty acids that have a variety of biological
effects.
Anti-depressants are substances capable of preventing or relieving depression.
Examples of anti-depressants include imipramine, amitriptyline, nortriptyline,
protriptyline, desipramine, amoxapine, doxepin, maprotiline, tranylcypromine,
phenelzine, and isocarboxazide.
Anti-psychotic substances are substances which modify psychotic behavior.
Examples of such agents include phenothiazines, butyrophenones and
thioxanthenes.
Anti-emetics are substances which prevent or alleviate nausea or vomiting. An
example of such a substance includes dramamine.
Imaging agents are agents capable of imaging a desired site, e.g. tumor, in
vivo.
Examples of imaging agents include substances having a label which is
detectable in vivo,
e.g. antibodies attached to fluorescent labels. The term antibody includes
whole
antibodies or fragments thereof.
Specific targeting agents include agents capable of delivering a therapeutic
agent to
a desired site, e.g. tumor, and providing a therapeutic effect. Examples of
targeting
agents include agents which can carry toxins or other agents which provide
beneficial
effects. The targeting agent can be an antibody linked to a toxin, e.g. ricin
A or an
antibody linked to a drug.
Neurotransmitters are substances which are released from a neuron on
excitation
and travel to either inhibit or excite a target cell. Examples of
neurotransmitters include
dopamine, serotonin, -y-aminobutyric acid, norepinephrine, histamine,
acetylcholine, and
epinephrine:
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Trophic factors, growth factors, and cell response modifrers are factors whose
continued presence improves the viability or longevity of a cell. In some
cases, they
produce chemotactic effects, or have protective effects against toxins or
neurotoxins, or
against neurodegeneration. Suitable such factors include, but are not limited
to,
platelet-derived growth factor (PDGF), neutrophil-activating protein, monocyte
chemoattractant protein, macrophage-inflammatory protein, platelet factor,
platelet basic
protein, and melanoma growth stimulating activity; epidermal growth factor,
transforming
growth factor (alpha), fibroblast growth factor, platelet-derived endothelial
cell growth
factor, insulin-like growth factor, glial derived growth neurotrophic factor,
ciliary
neurotrophic factor, nerve growth factor, and bone growth/cartilage-inducing
factor (alpha
and beta), or other bone morphogenetic proteins.
Other cell response modifiers are the interleukins, interleukin inhibitors or
interleukin receptors, including interleukin 1 through interleukin 10;
interferons, including
alpha, beta and gamma; hematopoietic factors, including erythropoietin,
granulocyte
colony stimulating factor, macrophage colony stimulating factor and
granulocyte-macrophage colony stimulating factor; tumor necrosis factors,
including alpha
and beta; transforming growth factors (beta), including beta-l, beta-2, beta-
3, inhibin, and
activin; and bone morphogenetic proteins such as OP-i, BMP-2 and BMP-7.
Hormones include estrogens (such as, for example, estradiol, estrone, estriol,
diethylstibestrol, quinestrol, chlorotrianisene, ethinyl estradiol,
mestranol), anti-estrogens
(such as, for example, clomiphene, tamoxifen), progestins (such as, for
example,
medroxyprogesterone, norethindrone, hydroxyprogesterone, norgestrel),
antiprogestin
(mifepristone), androgens (such as, for example, testosterone cypionate,
fluoxymesterone,
danazol, testolactone), and anti-androgens (such as, for example, cyproterone
acetate,
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flutamide). Hormones are commonly employed for hormone replacement therapy
and/or
for purposes of birth control. Steroid hormones, such as prednisone, are also
used as
immunosuppressants and anti-inflammatories. Delivery of steroid hormones can
be
delayed by esterification. Thyroid hormones include triiodothyronne,
thyroxine,
propylthiouracil, methimazole, and iodixode. Pituitary hormones include
corticotropin,
sumutotropin, oxytocin, and vasopressin.
Nucleic acids are molecules, including DNA or RNA molecules, that comprise one
or more nucleosides and/or nucleotides. Since calcium compounds are known to
promote
cell transfection and DNA uptake in some systems, it is anticipated that
resorption of the
present delivery device may improve transfection efficiency. Nucleic acid
molecules can
be delivered as vaccines or, for example, as antisense agents. Alternatively,
DNA
molecules can be prepared for use in gene therapy, in which molecules can
correct or
compensate for genetic errors in cells into which the DNA molecules are to be
introduced.
Standard protocols and regimens for delivery of the above-listed agents are
known
in the art. Typically, these protocols are based on oral or intravenous
delivery. To the
extent that the present invention provides for alternate delivery modes,
modification to
these protocols may be appropriate.
Biologically active agents are introduced into a delivery vehicle served from
PCA
material of the present invention during or after its formation (see Examples
20-21).
Agents may conveniently be mixed into the paste prior to setting.
Alternatively, the
vehicle may be shaped and hardened and then exposed to the therapeutic agent
in
solution. This particular approach is particularly well suited in proteins,
which are
known to have an affinity for apatitic materials. A buffer solution containing
the
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biologically active agent may be employed, instead of water, as the aqueous
solution in
which the amorphous calcium phosphate is converted into the synthetic, poorly
crystalline
apatitic material of the present invention. Buffers may be used in any pH
range, but most
often will be used in the range of 5.0 to 8.0 in preferred embodiments the pH
will be
compatible with prolonged stability and efficacy of the desired therapeutic
agent and, in
most preferred embodiments, will be in the range of 5.5 to 7.4. Suitable
buffers include,
but are not limited to, carbonates, phosphates (e.g., phosphate buffered
saline), and
organic buffers such as Tris, HEPES, and MOPS. Most often, the buffer will be
selected
for it's biocompatibility with the host tissues and its compatibility with the
therapeutic
agent. For most applications of nucleic acids, peptides or antibiotics a
simple phosphate
buffered saline will suffice.
Biologically active agents are introduced into the vehicle in amounts that
allow
delivery of an appropriate dosage of the agent to the implant site. In most
cases, dosages
are determined using guidelines known to practitioners and applicable to the
particular
agent in question. It is generally preferred, for those agents that bind to a
receptor, to
achieve local levels approximately 1-2 fold higher than the dissociation
constant of the
receptor-agent complex. Loading levels, device size, and resorption properties
can be
determined empirically through the use of animal models and human efficacy
studies, as
is common in the pharmaceutical industry.
One of the advantages of the present delivery material, as compared with
ceramic
devices generally, and with calcium phosphate materials in particular, is that
it can be
formed under mild reaction conditions. For example, although calcium phosphate-
based
ceramics (e.g., hydroxyapatites) have been much studied as potential drug
delivery
materials because of their biocompatibility and known affinity for protein
agents, such
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materials are typically prepared in processes that require have detrimental
effects on many
therapeutic agents. For example, some methods require sintering above 500 C,
others
require the use of acidic conditions, and still others require extended
periods of time to
grow crystals containing the therapeutic agent. By contrast, the present
synthetic PCA
drug delivery vehicle can be prepared at ambient temperatures and
physiologically
relevant pHs (see Example 4). Accordingly, a wide variety of biologically
active
materials that might be destroyed during the preparation of standard calcium
phosphate
materials can be incorporated into the drug delivery material of the present
invention.
Protein agents in particular are often sensitive to heat and other unfavorable
conditions;
the present synthetic PCA material therefore constitutes a particularly
improved delivery
system for protein agents.
Cells
Where the PCA material of the invention is to be utilized in a cell seeding
application, the hydrated precursor is preferably prepared with an aqueous
solution that is
a physiological medium. Examples of such media are well known in the art
(e.g.,
Dulbecco's minimal essential medium; phosphate buffered saline; and carbonate,
TRIS, or
HEPES-buffered solutions); and those of ordinary skill are aware of particular
media that
are compatible with desired cell types.
Of course, it is not essential that the hydrated precursor be prepared with a
buffered aqueous solution rather than water. However, as it is desirable to
maintain cell
viability, a hydrated precursor or hardened PCA material that has been
prepared using
water (or other minimal aqueous solution) will preferably be exposed to growth
medium
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prior to, or at least coincident with, its exposure to cells. Introduction of
a material into
an animal can constitute exposure of the material to growth medium (and to
cells).
The PCA material of the present invention may be prepared with any of a
variety
of additives, and/or may be prepared as a composite. For examples of desirable
PCA
material composites, see U.S. application entitled "Bioactive Ceramic
Composites" and
filed on even date herewith; for examples of biologically active materials
that can be
incorporated into the PCA material before or after cell seeding, see U.S.
application
entitled "Delivery Vehicle" and filed on even date herewith. In some cases, it
will be
particularly desirable to add factors to the PCA material that can affect cell
growth,
differentiation, and/or localization. For example, laminin, fibronectin,
collagen, matrigel
and its components, and other growth factors and extracellular matrix
components.
Cells
The PCA material of the present invention may be seeded with any of a variety
of
cells. A "cell", according to the present invention, is any preparation of
living tissue,
including primary tissue explants and preparations thereof, isolated cells,
cells lines
(including transformed cells), and host cells. Preferably, autologous cells
are employed,
but xenogeneic, allogeneic, or syngeneic cells are also useful. Where the
cells are not
autologous, it may be desirable to administer immunosuppressive agents in
order to
minimize rejection. In preferred embodiments, such agents may be included
within the
seeded composition to ensure effective local concentrations of the agents and
to minimize
systemic effects of their administration. The cells employed may be primary
cells,
explants, or cell lines, and may be dividing or non-dividing cells. Cells may
be expanded
ex-vivo prior to introduction into the inventive PCA material. Autologous
cells are
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preferably expanded in this way if a sufficient number of %iable cells cannot
be harvested
from the host.
Any preparation of living cells may be use to seed the PCA material of the
present
invention. For example, cultured cells or isolated individual cells may be
used.
Alternatively or additionally, pieces of tissue, including tissue that has
some internal
sttucture, may be used. The cells may be primary tissue explants and
preparations
thereof, cell lines (including transformed cells), or host cells. Where the
cells are host
cells and are introduced into the inventive PCA material in vivo (see below),
preferred
sources of cells include, but are not limited to, the inner layer of the
periosteum or
perichondrium, blood or other fluids containing the cells of choice, and
damaged host
tissue (particularly bone or cartilage) that includes such cells.
Any available methods may be employed to harvest, maintain, expand, and
prepare cells for use in the present invention. Useful references that
describe such
procedures include, for example, Freshney, Culture of Animal Cells: a Manual
of Basic
Technique, Alan R. Liss Inc., New York, NY.
The PCA material of the invention is useful as a scaffold for production of
hard or
soft tissues. Tissue-producing or -degrading cells that may be incorporated
into the
material include, but are not limited to, chondrocytes, osteocytes,
osteoblasts, osteoclasts,
mesenchymal stem cells, other bone- or cartilage-producing cells or cell
lines, fibroblasts,
muscle cells, hepatocytes, parenchymal cells, cells of intestinal origin,
nerve cells, and
skin cells.
Methods of isolating and culturing such tissue-producing or -degrading cells,
andlor their precursors, are known in the art (see, for example, Vacanti et
al., U.S.
Patent No. 5,041,138; Elgendy et al., Biomater. 14:263, 1993; Laurencin et
al., J.
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Biomed. Res. 27:963. 1993; Freed et al., J. Cell. Biochem. 51:257, 1993; Atala
et al.,
J. Urol. 150:745, 1993; Ishaug et al.. J. Biomed. Mater. Res. 28:1445, 1994;
Chu et al.,
J. Biomed. Mater. Res. 29:1147, 1995; Thomson et al., J. Biornater. Sci.
Polvmer Edn.
7:23, 1995).
For example. mesenchymal stem cells, which can differentiate into a variety of
mesenchymal or connective tissues (including, for example, adipose, osseous,
cartilagenous, elastic. and fibrous connective tissues), can be isolated,
purified, and
replicated according to known techniques (see Caplan et al., U.S. Patent No.
5,486,359;
Caplan et al., U.S. Patent No. 5,226.914; Dennis et al., Cell Transplantation
1:23, 1992).
Such mesenchymal cells have been
studied in association with tricalcium phosphate and hydroxyapatite carriers
and have been
found to be capable of successful differentiation from within such carriers
(see Caplan et
al., U.S. Patent Number 5,197,985). Similar
procedures are employed to direct mesenchymal cell differentiation within PCA
material
scaffolds of the present invention.
Of course, the present invention is not limited to the use of tissue-producing
cells.
Certain preferred embodiments of the invention utilize such cells, primarily
because the
inventive PCA material is so well suited to tissue-regeneration applications
(particularly
with those involving growth of bone and/or cartilage). Any cell may be seeded
into the
PCA material of the invention. In some cases, it will be desirable to include
other cells
in addition with tissue-producing cells.
The cells that are seeded into the inventive PCA material may be genetically
engineered, for example to produce a protein or other factor that it useful in
the particular
application. - In preferred embodiments, cells may be engineered to produce
molecules
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that impart resistance to host immune attack and rejection. The Fas-L and CR-1
genes
are examples of useful such genes.
Other coMonents
When the inventive PCA material is used in a cell seeding application, one or
more additives may be introduced into the PCA material before or after
seeding. In
certain preferred embodiments of the invention, one or more biologically
active agents is
incorporated into the PCA material. For discussion of such biologically active
agents and
their use in conjunction with the inventive PCA material, see U.S. application
entitled
"Delivery Vehicle" and filed on even date herewith.
Preferred biologically active agents for use in the seeded PCA material
compositions of the present invention include factors that influence cell
growth,
differentiation, migration, and/or localization. For example, bone matrix
contains a
variety of protein factors that influence cell behavior (see, for example,
Hubbell,
BiolTechnology 13:565, 1995; Caplan et al., U.S. Patent No. 4,609,551; Caplan
et al.,
U.S. Patent No. 4,620,327).
Also, cell matrix components can play important roles in division,
differentiation,
migration, and localization (see, for example, Hubbell, Bio/Technology 13:565,
1995). It
may therefore be desirable to localize such matrix components within the
seeded PCA
material of the present invention. However, many of the functions achieved by
association between cells and cell matrix components (e.g., definition of cell
shape,
achievement of cell polarity and organization, etc.) may well be accomplished
by cell
attachment directly to the inventive PCA material.
Other biologically active agents that are preferred for use in certain
embodiments
of the invention include nutrients, angiogenic factors, compounds that enhance
or allow
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ingrowth of the lymphatic network or nerve fibers, etc. Immunomodulatory
factors, and
particularly inhibitors of inflammation, may be included where it is desirable
to inhibit a
host response to the implanted composition. Drugs may also be included.
Generally, cells are introduced into the PCA material of the present invention
in
vitro, although in vivo seeding approaches are employed in some circumstances
(see
below). Cells may be mixed with the hydrated precursor paste or putty prior to
hardening or, alternatively, may be introduced into the PCA material
composition after it
has hardened. In either case, it is important that adequate growth (or
storage) medium be
provided to ensure cell viability. If the composition is to be implanted for
use in vivo
after in vitro seeding, sufficient growth medium must be supplied to ensure
viability
throughout, and for a short time following, the implant proceeding. Once the
composition has been implanted, the porous nature of the PCA material allows
the cells'
nutritional requirements to be met by the circulating fluids of the host.
We have found Dulbecco's minimal essential medium to be particularly useful in
the practice of the present invention. Other solutions that may be employed
include, but
are not limited to, phosphate-buffered saline; carbonate-, HEPES-, or TRIS-
buffered
solutions. In some cases, additional growth-stimulating components, such as
serum,
growth factors, amino acid nutrients, sugars, and salts, may be added to the
aqueous
solution employed in the present invention. However, it is generally desirable
to avoid
additives, as they can alter the hardening process of the inventive PCA
material. If a
particular collection of additives were selected to be used but had negative
effects on PCA
material characteristics, the precise PCA formulation can be varied and tested
for its
ability to satisfy hardening parameters in the presence of the additives.
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Any available method may be employed to introduce the cells into the PCA
material. In many cases, it will be desirable to introduce the cells into the
hydrated
precursor, before hardening. For example, cells may be injected into the
hydrated
precursor (preferably in combination with growth medium), or maybe introduced
by other
means such as pressure, vacuum, or osmosis. Alternatively (or additionally),
cells may
be layered on the hydrated precursor, or the hydrated precursor may be dipped
into a cell
suspension and allowed to remain there under conditions and for a time
sufficient for cells
to impregnate or attach to the material. Generally, it is desirable to avoid
excessive
manual manipulation of the cells in order to minimize cell death during the
impregnation
procedure. For example, in most situations it will not be desirable to
manually mix or
knead the cells with the PCA material paste; however, such an approach is
perfectly
useful in those cases in which a sufficient number of cells will survive the
procedure.
Cells may also be introduced into the hydrated precursor in vivo simply by
placing the
material in the body adjacent a source of desired cells. In some cases, it may
be
desirable to enhance such in vivo cell impregnation by including within the
material an
appropriate chemotactic factor, associative factor (i.e., a factor to which
cells bind), or
factor that induces differentiation of cells into the desired cell type.
Rather than being introduced into the hydrated precursor, cells may be
introduced
into the PCA material of the invention after it has hardened. Because the
material is
porous, cells are able to readily migrate into it. Cells may be introduced
into the
hardened PCA material by any available means. For example, cells may be
layered on
the material, or may be introduced by pressure, vacuum, or osmosis.
Alternatively (or
additionally), the hardened material may be placed in a cell suspension and
maintained
there under conditions and for a time sufficient for the cells to impregnate
the material.
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Furthermore, the hardened PCA material may be prepared with a mold or as a
composite
with a leachable material (e.g., sugars, salt crystals, or enzyme-degradable
fillers) to
provide seeding chambers or areas within the device. In such approaches, the
cells are
preferably introduced into these chambers through a pipette or a syringe.
Cells may also
be introduced into the inventive hardened PCA material in vivo, by placing the
material in
the body adjacent to a source of desirable cells or cell precursors as
described above for
the hydrated precursor. In preferred embodiments, the hardened material is
placed
adjacent the periosteum or perichondrium, or is exposed to blood, fluids, or
damaged host
tissue that contains the desirable cells.
As those of ordinary skill will readily appreciate, the number of cells to be
introduced into the inventive material (be it the hydrated precursor or the
hardened PCA
material) will vary based on the intended application of the seeded material
and on the
type of cell used. Where dividing autologous cells are being introduced by
injection into
the hydrated precursor, use of 20,000 - 1,000,000 cells per cm3 are expected
to result in
cellular proliferation and extracellular matrix formation within the material.
Where non-
dividing cells are employed, larger numbers of cells will generally be
required. In those
cases where seeding is accomplished by host cell migration into the material
in vivo,
exposure of the material to fluids containing cells (e.g., bone-forming
cells), or to tissue
(e.g., bone) itself has proven to be effective to seed the material with cells
without the
need for inoculation with a specified number of cells.
Modification of Delivery Kinetics
One advantage of the PCA material present invention is that the rate of
resorption
of the material can be modulated through modifications in the preparative
methods.
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Specifically, methods that lead to a more dense hardened product will
generally result in a
slower resorption time of the pure inventive PCA calcium phosphate in vivo. In
this
regard, there are a variety of ways to alter the density or resorption
kinetics of the
hardened product. These include adjustment of the volume of liquid used to
create the
paste, alteration of grain size of the starting materials, and compression of
the paste
during hardening. Composites, in which leachable or biodegradable particles or
materials
are incorporated into the paste, and ultimately the hardened PCA material, may
also be
prepared. The leachable or biodegradable materials may subsequently be removed
(e.g.,
by leaching) from the hardened material in vivo, so that a highly porous
implant is
produced. Additionally, the inventive PCA material may be prepared with a
distribution
of densities within the same implant. One way this may be accomplished is by
preparing
in vitro-hardened PCA material of one density, pulverizing the hardened
material to a
desired grain size, and then mixing the pulverized material with a second PCA
material
paste designed to produce a different density PCA material. PCA materials made
in this
way will resorb asynchronously.
The use of overall smaller grain size material to prepare the PCA material
precursor powder results in a longer time to resorb and/or reossify in vivo
(see Examples
5 and 19). Since the ACP precursor is generally prepared at a very small grain
size,
when two components are used to produce the inventive vehicle, the grain size
of the
other non-ACP component is generally used to adjust resorption time. In this
regard, the
grain size may be adjusted by using a ground and sieved second component to
select a
specific grain size distribution for addition to the final mixture. In another
embodiment,
the second component is ground with the ACP for varying amounts of time to
affect the
resorption rate.
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Composite materials with altered resorbability kinetics are produced by
incorporating into the PCA material an "erosion rate modifier", which is a
material whose
presence alters the rate of resorbability of the device as a whole. Erosion
rate modifiers
that increase the rate at which the drug delivery device resorbs include any
leachable or
biodegradable compound that affects the solubility (e.g., by altering the
porosity) of the
device over time in vivo. Erosion rate modifiers that decrease the rate at
which the drug
delivery device resorbs include crystalline calcium phosphates, particularly
hydroxyapatite, and diphosphate compounds.
Another way that the rate of resorption of the inventive PCA material can be
modulated is through the action of osteoclast and/or macrophage cells.
Osteoclasts, and
possibly macrophages, naturally digest bone. According to the present
invention, osteoclast
or macrophage cells, or factors that modulate their development and/or
activity, can be
administered in conjunction with an inventive PCA material implant to
accelerate or retard
the rate of PCA material resorption.
For example, any agent that directly or indirectly (e.g., through osteoblasts)
stimulates
osteoclast activity or development may be employed to increase the resorption
rate of a PCA
material implant. Conversely, any agent that directly or indirectly inhibits
osteoclast activity
or development may be employed to reduce the resorption rate of an implant.
Such
stimulatory and inhibitory agents are well known in the art (see, for example,
Athanasou, J.
Bone Joint Surg., 78-A: 1096, 1996 and Roodman Endocrine Rev. 17:308, 1996,
each of
which is incorporated herein by reference). For example, interleukin-1 (IL-1),
colony
stimulating factors (CSFs) such as macrophage (M)-CSF, transforming growth
factor a
(TGFa), tumor necrosis factor (TNF), interleukin 6 (IL-6), interleukin- 11 (IL-
11),
interleukin-3 (IL-3), para-thyroid hormone (PTH), vitamin D3 metabolites
(e.g., calcitriol),
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prostaglandins (under certain, known conditions), and oxygen free radicals are
known to
stimulate osteoclast development and/or activity. Where CSFs are utilized,
subsequent
administration of 1,25-dihydroxyvitamin D3 can further stimulate osteoclasts;
by contrast,
concomitant administration of colony stimulating factors and 1,25-
dihydroxyvitamin D3
inhibits osteoclast.
Other factors that inhibit osteoclast development and/or activity include
transforming
growth factor-P (TGFP), y-interferon, interleukin-4 (IL-4), nitric oxide,
antibodies, for
example, against the osteoclast vitronectin receptor, calcitonin, and
prostaglandins (under
certain, known conditions).
Of course, it is also possible to introduce osteoclasts themselves (or
osteoclast
precursor cells, preferably in combination with agents that stimulate their
differentiation into
osteoclasts) into a PCA material implant in order to stimulate its resorption.
Agents that alter PCA material resorption rate may be administered
systemically or
locally. Local administration is preferably accomplished by introducing the
agent into, or
associating the agent with, the material itself, preferably according to the
procedures
described herein. Where local administration is being employed, it is
preferred that diffusion
of the agent away from the PCA material implant be minimized. For example,
relatively
insoluble agents are preferred because it is less likely that they will
diffuse away from the
implant and exert undesirable effects on other cells within the body.
Applications
As alluded to above, the cell seeded PCA material of the present invention
can be usefully employed in any of a variety of in vivo and in vitro systems.
For
example, the material may be used to deliver biologically active agents or
cells to any of
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a variety of sites in a body (preferably a human body, though veterinary
applications are
also within the scope of the invention. Alternatively or additionally, the
material may be
used in bone tissue or repair applications or augmentation plastic therapy in
vivo. The
material may also be employed as a cell encapsulation membrane or matrix, or
in
artificial organ construction or repair.
In vitro, the material may be used as a three dimensional cell culture matrix,
and
as a model for analyzing osteoclast, osteoblast, chondrocyte, and/or
macrophage cultures,
progenitor cell differentiation, and/or reossification and calcium phosphate
resorption.
The material is particularly useful for tissue formation and/or degradation
studies, for
example employing cells such as progenitor cells, stem cells, osteocytes,
osteoclasts,
osteoblasts, chondrocytes, macrophages, myoblasts, and fibroblasts. The
material may
also be employed to accomplish in vitro delivery of a biologically active
agent.
Certain preferred applications are discussed in more detail below, but the
discussion is intended only for purposes of exemplification and is not
intended to be
limiting.
When used as an in vivo or in vitro delivery vehicle, the PCA material of the
present invention offers the advantage of controlled, localized delivery. As
is well
known, smaller amounts of biologically active agent are required when the
agent is
delivered to a specific site rather than administered systemically.
Furthermore, potential
toxic side effects of the agent are minimized when the agent is delivered from
the
delivery vehicle of the present invention. Also, the agent's activity is
maximized because
it is protected within the delivery vehicle until it is delivered to its site.
The PCA material of the present invention can be injected or implanted into
any
acceptable tissue. Oral formulations are also considered within the scope of
the
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invention. Preferred delivery sites include sites in bone, muscle, the spinal
cord, the
central nervous system, the interperitoneal cavity, subcutaneous locations,
and the
vitreous and aqueous humor of the eye. When the PCA material is delivered to a
site
under circumstances where implant migration is a concern, anchoring sutures or
hooks
may be incorporated into the vehicle so that it can be attached and maintained
in position.
When appropriate, the PCA material may be anchored by insertion into a bony
site (see
below). Particular applications and preferred delivery sites are discussed in
more detail
below:
Delivery of Bilogically Active Agents to Bony Sites
The PCA material of the present invention has particular advantages for
delivery
of biologically active agents to sites in bone. Implantation of a delivery
vehicle formed
from PCA material of the present invention in a bony site may alternatively or
additionally be utilized to anchor a delivery vehicle and accomplish systemic
drug
delivery, or may be utilized to accomplish delivery to a site adjacent to,
though not
strictly speaking "within", the bone. Figure 9 depicts many useful
applications of the
PCA material of the present invention in bony sites.
Naturally-occurring bone mineral is made of nanometer-sized, poorly-
crystalline
calcium phosphate with apatitic structure. However, unlike the ideal
stoichiometric
crystalline hydroxyapatite, Calo(PO4)6(OH)Z, with atomic Ca/P ratio of 1.67,
the
composition of bone mineral is significantly different and may be represented
by the
following formulae,
Ca8.3 (P04)4.3 (HPO4 ,C03)1.7 (OH, CO3)0.3-
Bone mineral non-stoichiometry is primarily due to the presence of divalent
ions,
such as C03Z- and HP04Z-, which are substituted for the trivalent P043- ions.
Substitution
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by HPO42- and C032- ions produces a change of the Ca/P ratio, resulting in
Ca/P ratio
which may vary between 1.50 to 1.70, depending on the age and bony site.
Generally,
the Ca/P ratio increases during aging of bone, suggesting that the amount of
carbonate
species typically increases for older bones. It is the Ca/P ratio in
conjunction with
nanocrystalline size and the poorly-crystalline nature that yields specific
solubility
property of the bone minerals. And because bone tissues undergo constant
tissue repair
regulated by the mineral-resorbing cells (osteoclasts) and mineral-producing
cells
(osteoblasts), solubility behavior of minerals is important in maintaining a
delicate
metabolic balance between these cells activities.
The PCA material of the present invention is a nano-size, poorly crystalline
solid
with a Ca/P ratio comparable to that of natural bone minerals. The material is
bioresorbable, can be produced at low temperatures, and is readily formable
and
injectable. For all of these reasons, the inventive material is particularly
well suited for
drug delivery in bony sites. Furthermore, this synthetic PCA material can
support bone
growth so that it is eventually replaced by the patient's own bone. It should
be borne in
mind, however, that bone ingrowth may well affect the resorbability rate of
the drug
delivery material of the present invention. Accordingly, it may be desirable
in certain
circumstances (e. g. , where the biologically active agent must be delivered
according to a
precise, predetermined administrative schedule) to reduce bone growth into the
drug
delivery vehicle, for example by blocking penetration of osteocytic or
chondrocytic cells
or precursors. In most circumstances, ossification can be avoided by placing
the device
at some distance away from bone. Generally, 1 mm will be sufficient, although
greater
distances are preferred. Also, compounds such as Indian hedgehog gene and gene
products, parathyroid hormone-related protein (PTHRP) and PTHRP receptor
agonists
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may be included in, on, or adjacent to the drug delivery device in order
prevent bone
growth.
In other circumstances, such bone ingrowth can desirably be encouraged. As
shown in Examples 14, 17, and 18, the PCA calcium phosphate material can be
placed
into bony sites and allowed to resorb in a manner that results in its apparent
complete
(100%) replacement with new bone. Where optimal ossification is desired, the
devices
and objects may be seeded with bone forming cells (see below). This goal is
most easily
accomplished by placing the device in contact with a source of the patient's
own bone
forming cells. Such cells may be found in bone tissue or in bone-associated
blood or
fluids, including exogenous fluids which have been in contact with bone or
bone materials
or regions, including the periosteum, cancellous bone or marrow. In the case
of devices
such as screws and pins, the introduction of which into bone is accompanied by
bleeding,
no further seeding is required. For plates, which oppose only cortical bone,
induction of
a periosteal lesion which will contact the device is recommended. In yet other
embodiments, it will be useful to surgically prepare a seating within the bone
by
removing a portion of cortical bone at the implant site. Other steps may also
be taken to
augment ossification, including introduction bone forming cells harvested from
the patient
into the graft, or incorporation of trophic factors or bone growth inducing
proteins into,
or onto the device. Non-autologous bone cells are also within the scope of the
invention
if the desired amount of bone regeneration occurs prior to host rejection of
the bone
forming cells. In this regard, immunosuppressants may be administered to the
device
recipient, in some cases by incorporation into the device. Thus, cells or
tissues obtained
from primary sources, cell lines or cell banks may all be useful in certain
embodiments.
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Certain categories of biologically active agents are expected to be
particularly
suitable for delivery to bony sites. For example, where the drug delivery
vehicle is
applied to a damaged bone site, it may be desirable to incorporate bone
regenerative
proteins (BRPs) into the vehicle. BRPs have been demonstrated to increase the
rate of
bone growth and to accelerate bone healing (see, for example, Appel et al.,
Bzp. Opin.
Ther. Patents 4:1461, 1994). Exemplary BRPs include, but are in no way limited
to,
Transforming Growth Factor-Beta (TGF-0), Cell-Attachment Factors (CAFs),
Endothelial
Growth Factors (EGFs), OP-1, and Bone Morphogenetic Proteins (BMPs). Such BRPs
are currently being developed by Genetics Institute, Cambridge, MA; Genentech,
Palo
Alto, CA; and Creative Biomolecules, Hopkinton, MA. Bone regenerative proteins
and
trophic factors can also be used to stimulate ectopic bone formation if
desired. The
inventive PCA material containing BMP-7 can be placed subcutaneously, and bone
formation will occur within 1-2 months.
Antibiotics and antiseptics are also desirably delivered to bony sites using
the PCA
drug delivery vehicle of the present invention. For example, one of the major
clinical
implications arising from bone-graft surgery is a need to control the post-
operative
inflammation or infection, particularly infection associated with
osteomyelitis. An
embodiment drug delivery device of the present invention, including an
antibiotic, could
be used as (or in conjunction with) an improved bone graft to reduce the
chances of local
infection at the surgery site, contributing to infection-free, thus faster,
bone healing
process. The efficacy of antibiotics is further enhanced by controlling the
resorption of
the poorly crystalline hydroxyapatite such that it dissolves at a rate that
delivers antibiotic
peptides or its active component at the most effective dosage to the tissue
repair site.
Exemplary antibiotics include, but are in no way limited to, penicillin,
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tetracycline, kanamycin, gentamycin, chlortetracycline hydrochloride
(aureomycin),
minocyline, dosycycline, vanomycin, bacitracin, neomycin, erythromycin,
streptomyan,
cephalosporins, chloramphenicol, oxytetracycline (terramycine), and
derivatives thereof.
Antibiotics and bone regenerating proteins may be incorporated together into
the PCA
material of the present invention, to locally deliver most or all of the
components
necessary to facilitate optimum conditions for bone tissue repair.
Other biologically active agents that are desirably delivered to bony sites
include
anti-cancer agents, for example for treatment of bone tumors (see, for
example, Otsuka et
al., J. Pharm. Sci. 84:733, 1995). The drug delivery vehicle of the present
invention is
particularly useful, for example, where a patient has had a bone tumor
surgically removed
because the synthetic, PCA material of the present invention can improve the
mechanical
integrity of the bone site while also treating any remaining cancer cells to
avoid
metastasis. Exemplary anti-cancer agents include, for example, methotrexate,
cisplatin,
prednisone, hydroxyprogesterone, medroxyprogesterone acetate, megestrol
acetate,
diethyistiibestrol, testosterone propionate, fluoxymesterone, vinblastine,
vincristine,
vindesine, daunorubicin, doxorubicin, hydroxyurea, procarbazine,
aminoglutethimide,
mechlorethamine, cyclophosphamide, melphalan, uracil mustard, chlorambucil,
busulfan,
carmustine, lomusline, dacarbazine (DTIC: dimethyltriazenomidazole
carboxamide), fluorouracil, 5-fluorouracil, cytarabine, cytosine arabinoxide,
mercaptopurine, 6-mercaptopurine, thioguanine.
Additional biologically active agents that can desirably be incorporated into
the
synthetic PCA drug delivery system of the present invention for delivery to
bony sites are
agents that relieve osteoporosis. For example, amidated salmon calcitonin has
been
demonstrated to be effective against osteoporosis.
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Vitamin D and V itamin K are also desirably delivered to bony sites, as are
angiogenic factors such as veg f, which can be used when it is desirable to
increase
vascularization.
Bone Production and Healing
In preferred embodiments of the present invention, the PCA material is seeded
with bone-formina cells or precursors thereof. Preferably, the PCA material is
formulated, and the cell population is selected, so that the PCA material
becomes ossified
within a period of about 4-12 weeks.
In particularly preferred embod'unents of the invention, the seeding is
accomplished by placing the PCA material in contact with a source of the
host's own
bone-producing cells. Such cells are found in bone tissue or in bone-
associated blood or
fluids, including exogenous fluids that have been in contact with bone
(including
cancellous bone), bone materials, or bone regions such as the periosteum or
the marrow.
Where the PCA material is to be implanted
into a bony site in vivo in a manner that induces bleeding, such bleeding can
effectively
introduce bone-forming cells into the material so that no further seeding is
required.
Approaches that induce bleeding include those in which the PCA material is
formed into a
screw or pin, or is applied in conjunction with a screw or pin made from
another
material.
Where the PCA material is used as or in conjunction with a plate that opposes
only cortical bone, it is preferred that a periosteal lesion be introduced in
a manner that
creates contact between the PCA material and the lesion, so that cells may
penetrate into
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the PCA material from the lesion. Similarly, in some embodiments of the
invention, it
will be useful to surgically prepare a PCA device seating within the bone by
removing a
portion of cortical bone at the implant site. Cells at the implant site will
migrate into and
seed the PCA material.
- Of course, it is not required that the PCA material devices be seeded by in
vivo
impregnation of the host's own cells. Bone forming cells harvested from the
host may be
introduced in vitro into the device, so that a seeded composition is implanted
in the host.
Furthermore, seeding with non-autologous bone cells is also within the scope
of the
invention, but care must be taken to ensure that a desired amount of bone
growth occurs
prior to host rejection of the bone forming cells. Such non-autologous cells
can be
obtained from any of a variety of sources, including but not limited to
primary sources,
cell lines, and cell banks.
Bone formation in and around the PCA material can be enhanced by the
incorporation of trophic factors and/or bone-growth inducing factors into, or
onto, the
PCA material device.
Osseous Augmentation
Seeded PCA compositions of the present invention are useful for the
enhancement
or alteration of the shape of bony structures (e.g., a chin). For such
applications, the
PCA material may be supplied either as a pre-hardened shape or a molded putty
form and
applied to a bony surface. Generally, PCA material formulations selected for
augmentation applications will be those that resorb on a relatively slower
time course,
typically requiring 6-12 weeks for resorption.
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PCA material employed in augmentation applications are typically seeded
through
application of cells or cell lines to the PCA material, although some
preferred
embodiments involve host cell seeding. The term "host cell seeding"
encompasses any
method by which cells of the host are introduced into the PCA material. For
example,
the term encompasses migration of host cells into a device implanted in vivo,
as well as
assisted migration accomplished by placing bone blood or fragments of the
periosteum on
or in contact with the device (in vivo or in vitro), among other things.
Cartilage Production and Healing
Damage to cartilage can result in serious physical deformations. Currently,
the
most common treatment for loss of cartilage is replacement with a prosthetic
material, but
many difficulties have been encountered with this approach. As put by one of
the leaders
in the field, "The lack of truly biocompatible, functional prostheses can have
profound
and tragic effects for those individuals who have lost noses or ears due to
burns or
trauma". Seeded PCA compositions of the present invention offer an attractive
alternative
in which the PCA material acts as a formable scaffold into and within which
tissue can
grow. The PCA material is bioresorbable so that, eventually, the PCA material
implant
can be replaced with natural tissue; the negative effects of long-term
prosthetic implants
can therefore be avoided.
The PCA material of the present invention can be seeded with cartilage-forming
cells in order to optimize chondrogenesis. Preferably, this seeding is
accomplished by
placing the device in contact with a source of the host's own cartilage-
forming cells (e.g.,
chondrocytes) or precursors thereto. Such cells are found in cartilage-
associated blood or
fluids, including exogenous fluids that have been in contact with cartilage or
cartilagenous
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materials. Thus, fluids that have been in contact with the perichondrium,
cartilage, or
marrow typically contain such cells.
In many cases, e.g., a PCA material device designed for augmentation of a
damaged ear, seeding can be accomplished by placing the PCA device in contact
with the
breached region of the perichondrium. In other cases, it will be useful to
surgically
prepare a seating for the PCA device within existing cartilagenous tissue by
removing a
portion of the cartilage at the implant site.
In some embodiments of the present invention, additional steps may be taken to
augment chondrogenesis associated with the seeded PCA material. For example,
cartilage-forming cells harvested from the patient may be introduced into the
device in
addition (or as an alternative to) cells that impregnate it after implantation
in vivo.
Alternatively or additionally, trophic factors or cartilage growth-inducing
factors may be
incorporated into or onto the device.
It should be clear that autologous cells are not required for the seeded PCA
compositions employed in cartilage-forming applications; non-autologous cells
are also
within the scope of the invention so long as the cells are selected and the
PCA material is
formulated so that a desired amount of cartilage regeneration occurs prior to
host
rejection of the cartilage-forming cells. Thus, cells or tissues obtained from
primary
sources, cells lines, or cell banks are useful in the practice of this
embodiment of the
present invention.
Ectopic Bone or Cartilage Production
The seeded PCA material compositions of the present invention can be used to
produce bone or cartilage formation at a site at which bone or cartilage does
not normally
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occur. Introduction of a PCA composition into which bone- or cartilage-
producing cells
have been seeded into an in vivo implant site will result in bone or cartilage
formation at
that site. In preferred embodiments, the PCA material contains growth and/or
trophic
factors in addition to the seeded cells, so that maintenance of the
ectopically-formed bone
or cartilage can be prolonged. Once it has been produced, such ectopic tissue
may either
be left in place or may be surgically removed, depending on its intended use.
Aiternatively or additionally, trophic or growth factors external to the
implant may be
provided, e.g., through the use of encapsulated cells, polymer implants, or
other method
of factor delivery (see, for example, Aebischer et al., U.S. Patent No.
4,892,538; Sefton,
U.S. Patent No. 4,353,888 and Winn et al. Experimental Neurology 140:126
(1996)).
Ectopic tissues may be formed in vitro using inventive seeded PCA material
compositions. Preferably, a hydrated precursor is prepared, is shaped by hand
or through
the use of a mold or form, and is subsequently hardened at an elevated
temperature (27-
50 C). Alternatively, the PCA material may first be hardened and subsequently
be
machined or otherwise formed into a desired shape. Cell seeding can be
accomplished by
any of the methods described herein, so that ectopic tissue will be formed in
vitro in the
desired shape. Generally, to ensure that the shape is maintained during cell
growth, it
will be desirable to inhibit the action of degredative enzymes and cells, as
is known in the
art.
Cell Encapsulation Matrix
The PCA material of the present invention provides an excellent growth matrix
for
use within the cell encapsulation environment. Use of this material can
prevent cell
settling, provide cell dispersion, and optimize nutrient localization by
encapsulated cells.
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Thus, according to the invention, cells may be encapsulated within
encapsulation devices
in the presence of the hydrated precursor or hardened PCA of the present
invention, and
the resultant encapsulated devices may then be implanted in vivo for use in
encapsulated
cell therapy applications. Useful techniques for preparing and using cell
encapsulation
devices are described in, for example, Winn et al., Expt. Neurol. 140:126,
1996 and
Aebischer, U.S. Patent No. 4,892,538; Sefton, U.S. Patent No. 4,353,888, and
Kordower et al., Cell Transplantation, 14:155, 1995, each of which is
incorporated
herein by reference.
Research Applications
The PCA material of the present invention, due to its ease of preparation,
mild
formation conditions, sparing solubility in most aqueous systems, and
tractability for use
in cell-embedding applications, provides an attractive three-dimensional
growth matrix for
use in research and production tissue culture applications. Furthermore, the
material is
useful for tissue formation and/or degradation studies (e.g., of bone or
cartilage).
Preferably, the material employed in such studies in seeded with cells such as
(but not
limited to) progenitor cells, stem cells, osteocytes, osteociasts,
osteoblasts, chondrocytes,
macrophages, myoblasts, and fibroblasts.
Diagnostics
Cell-seeded PCA materials of the present invention may be employed in
diagnostics that detect various health or disease states. For example, the
inventive PCA
material can be used in qualitative or quantitative assays to determine the
bone- or
cartilage-forming potential of cells taken from a patient to be diagnosed. The
inventive
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material can also be used in diagnostics to assay vascularization and hard
tissue
degradation. Various soft tissue diagnostics are also made possible with the
inventive
PCA material compositions.
Delivery of Biologically Active Agents to Subcutaneous Implant Sites:
Application of the present drug delivery device is not limited to bony sites,
of
course. In non-bony sites, the device is known resorb without ossification.
Placement of the instant delivery device subcutaneously is particularly useful
for
more systemic administration of biologically active compounds. The
administration of
estrogens and/or progesterones for the used in fertility control is an example
of a
subcutaneous application. Additionally, the administration of antigens and/or
vaccines
may be accomplished through subcutaneous implantation.
Delivery of Biologically Active Agents to Central Nervous System:
The delivery of therapeutic substances to the central nervous system may be
accomplished with the inventive delivery vehicles. Useful therapeutic
substances include
the delivery of ry-aminobutyric acid to epileptic foci, the delivery of L-dopa
or dopamine
in the striatum or substantia nigra for the treatment of Parkinson's disease,
the delivery of
growth factors for the prevention of neural degeneration such as GDNF in the
lateral
ventricles, striatum or substantia nigra for the treatment of Parkinson's
disease, the
administration of NGF to cortical and other regions for the treatment of
Alzheimer's
disease, or the administration of CNTF to the sacral or lumbar spinal cord for
the
treatment of amyelolateral sclerosis.
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Other: Delivery of Biologically Active Agents to sites.
Other potential delivery sites include intramuscular, interperitoneal, and
occular
areas.
Examples
Example 1: Preparation of Reactive Amorphous Calcium Phosphate
This -example describes the step-by-step preparation and methods to render
relatively inert amorphous calcium phosphate solids into a highly reactive
amorphous
calcium phosphate of the present invention.
Solution A was prepared at room temperature by the rapid dissolution of 55 g
Na2HPO4=7HZO (sodium phosphate), 50 g NaOH (sodium hydroxide), 30 g NaHCO 3,
(sodium bicarbonate) and 2 g Na4PZOZ= 10H20 in 1.3 1 of distilled water.
Solution B
was prepared at room temperature by rapid dissolution of 43 g Ca(N03)2=4H,O
(calcium
nitrate tetrahydrate) and 1 g MgCIZ=6Hz0 in 0.5 1 of distilled water.
The inert carbonated amorphous calcium phosphate was then prepared at room
temperature by the rapid addition of solution B to rapidly stirring solution
A. The
precipitate of gel-like amorphous calcium phosphate thus formed was
immediately filtered
using filter paper (0.05 sq. m) with medium filter speed and a vacuum pressure
of about
10-2 torr. The material formed a thin cake and was washed with approximately 4
liters of
distilled water by adding water into the filtrating funnel. The washed
material was then
collected using spatula and immersed into a liquid nitrogen in a 2.5 L
container.
Following the formation of hard frozen pieces, the container was transferred
into a
vacuum chamber for 24 hrs (10' - 10-2 torr), until a fine and dry powder was
obtained.
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Although the procedure described above may be performed at room temperature,
the entire process preferably takes place below ambient temperature (4-5 C),
so as to
further prevent the amorphous state from converting into more stable
crystalline form.
Further, such elements or ions known to act as inhibitors of crystalline
hydroxyapatite
formation may be added into the solution in trace amounts.
An infrared spectrum of the inert amorphous material at this point in the
process
contains peaks characteristic of P-0 groups (600 and 1000 cm' ), C032- group
(1,420-
1,450 cm-') with relatively large peak of 0-H group (- 3,550 cm-' ). X-ray
diffraction
pattern of the same material show amorphous nature of the material as
demonstrated by
absence of any sharp peaks when the measurement of crystallinity is determined
by taking
ratio of coherent peaks to background.
The inert amorphous material described above was then made into a reactive
form
by heating for 60 minutes at 450 C ( f 3 C) . The IR of the heated material
(not shown)
shows reduction of particular 0-H and C032_ groups, indicating significant
reduction of
H20 and C032- as CO, and H20. In similarly prepared samples the carbon content
was
observed to drop approximately 60% with a total carbonate ratio decreasing
from 1.56%
to 0.5%. Note, however, that the amorphous nature of the material was not lost
during
this process, as demonstrated by the X-ray diffraction pattern shown in Figure
4(a). The
Ca/P ratio measurement of this material after the heat treatment was
determined to be
1.575, using a method of quantitative electron microprobe analysis (Figure 2).
The
overall morphological and ultrastructural properties of amorphous material is
shown in
Figure 1, as seen under a transmission electron microscope. Note the
"amorphous"
appearance of the material with absence of sharp edges separating each
granules with
certain portion of the material to exhibit shapeless form (arrows). An
extremely high
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specific surface area of 120 m2/g, with an average pore size of approximately
130 A was
observed in this material.
ExamQle 2: Preparation of Reactive Amorphous Calcium Phosphate
The preparation was conducted as described in Example 1 above, with the
exception that the preparation of Solutions A and B was replaced by the
following
reactions. Solution A was prepared at room temperature by the rapid
dissolution of 90.68
g of Ca(N03)2=4H20 in 1.2 liter of carbonated distilled H20. Solution B was
prepared by
dissolving 40.57 g of K2HPO4 in 1.53 liters of distilled H20, containing 24 ml
of 45
vol. % KOH solution. Chemical and physical properties of the product amorphous
calcium phosphate resulting from this procedure were similar to those of the
material
prepared accordingly for Example 1.
Example 3: Preparation of Reactive Amorphous Calcium Phosphate
The preparation was conducted as described in Example 1 above, with the
exception that the preparation of Solutions A and B were replaced by the
following
reactions. Solution A was prepared at room temperature by the rapid
dissolution of 10.58
g of Ca(N03)2.6H20 in 0.15 liters of carbonated distilled HP at pH greater
than 9.0, as
adjusted by NaOH. Solution B was prepared by dissolving 7.8 g of (NH4)ZHPO4 in
0.35
liters of distilled H20. Chemical and physical properties of the product
amorphous
calcium phosphate resulting from this procedure were similar to those of the
material
prepared according to Examples 1 and 2.
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Example 4: Preparation of Synthetic Poorly Crystalline Apatitic Material from
Reactive
Amorphous Calcium Phosphate
This example describes the preparation of PCA material of the invention.
The dicalcium phosphate dihydrate (DCPD) used in this example was prepared in
the following manner. Solution A was prepared at room temperature by rapid
dissolution of 10 g H9NZO4P (diammonium hydrogen phosphate) in 500 ml
distilled water
at a pH of 4.6-4.8.
Solution B was prepared at room temperature by the rapid dissolution of 17.1 g
Ca(N03)2.4H20 (calcium nitrate tetrahydrate) in 250 mt distilled water. The
dicalcium
phosphate dihydrate was prepared at room temperature by the rapid addition of
solution B
to the stirring solution A. Immediately thereafter, the sample was filtered
using filter
paper (0.05 sq. m) with medium filter speed and a vacuum pressure of about 10-
1 torr.
The material formed a thin cake which was washed with about 2 liters of
distilled water
and then air dried at room temperature for 24-72 hrs.
The reactive amorphous calcium phosphate material prepared from Example 1 was
physically diy-mixed with dicalcium phosphate dihydrate (CaHPO4=2H2O) at 50:50
wt%
using a mortar and pestle for 3-5 min. Water (1 mi/g of mixed material) was
then added
to the powder mixture to yield a paste-like consistency. The amount of H20
added
varied, depending on whether a thick or thin paste was desired. The paste
material was
then wrapped in moist tissue paper and was hardened into a solid mass by
heating 37 C.
The hardening process could be delayed for several hours by wrapping the
sample in
parafilm and holding it at 4 C. Also, hardening can be allowed to proceed at
ambient
temperature, although setup times may then be expanded.
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The hardened material was composed of nanometer-sized, poorly crystalline
apatitic calcium phosphate with an inherent solubility property that exceeded
reported
solubilities for a synthetic hydroxyapatite material. This is demonstrated in
Figure 3,
where the concentration of calcium ions released into a controlled pH buffer
solution over
24 hrs at 37 C, was significantly higher for the PCA material of the present
invention
(curve 50) than the standard crystalline hydroxyapatite material (curve 52).
Example 5: Preparation of Synthetic, Poorly Crystalline Material from
Precursors of
Selected Particle Size
This example demonstrates the preparation of synthetic PCA materials using
precursors having a selected particle size.
DCPD was prepared as described in Example 4. The dry material was ground for
5 minutes in a SPEX 8510 laboratory mill with a SPEX 8505 alumina ceramic
grinding
chamber. Following grinding the material was serially sieved through a Tyler
test sieve
shaker to produce DCPD with 8 different grain size distributions as indicated
in Table 1.
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Table 1
DCPD Grain Size Distribution
Sample Grain Size Extent of
Distribution hardening at
30 min, 37 C
10-1 <25 m hard
10-2 25-35 m hard
10-3 35-53 m hard
10-4 53-63 m hard
10-5 distribution B3 hard
10-6 106-125 m not fully
hardened
10-7 distribution B2 not fully
hardened
10-8 unsieved not fully
distribution B1 hardened
It has been found that the preliminary grinding of DCPD prior to sieving can
be
replaced by a brief hand grinding using a mortar and pestle without
substantially
changing the results.
The reactive amorphous calcium phosphate material prepared from Examples 1, 2,
or 3 was physically dry-mixed 1:1 (wt/wt) with DCPD for 10 minutes using a
SPEX 8510
laboratory mill with a SPEX 8505 alumina ceramic grinding chamber. Water (1.0 -
0.8
mi/gm of dry mix) was then added to the powder mixture to yield a paste-like
consistency. 5 of the 8 samples indicated in Table 1 hardened well in 30
minutes at 37
C. Samples 6, 7 and 8 did not harden as quickly or as firmly as the other
samples.
Each of these samples had significantly higher percentages of > 100 m
particles than did
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the other samples. It is concluded from these observations that the use of
smaller grain
size DCPD leads to more rapid and complete hardening within larger grain size
DCPD.
Example 6: Preparation of Synthetic PCA Material from Reactive Amorphous
Calcium
Phosphate
Reactive amorphous calcium phosphate material as prepared in Examples 1 was
dry-mixed with other calcium phosphate compounds, according to the method
described in
Example 4. These compounds included, but were not limited to: Ca(P03)2
(calcium
metaphosphates), Ca7(P5016)2 (heptacalcium decaphosphate), Ca zP ZO, (calcium
pyrophosphate), Ca3(PO4)Z (tricalcium phosphates). The dry-mixture ratio was
properly
calculated to be between Ca/P ratios of 1.5-1.70, depending on the molar Ca/P
ratio of
the compound mixed with the reactive amorphous calcium. The resulting material
was
poorly crystalline apatitic calcium phosphate solids with solubility
properties same as
shown in Figure 3.
Example 7: Preparation of an Injectable Paste for Formation of a Synthetic,
PCA
Material from a Reactive, Amorphous Calcium Phosphate
This example describes the preparation of an injectable paste for the
formation of
poorly crystalline apatitic calcium phosphate solid.
The dried mixed materials prepared according to Examples 4 or 6 were mixed
with distilled H2O (2.3 ml/g). A paste was formed that could be easily shaped
by hand or
injected through a nozzle as small as 0.5 mm ID. The flowability increased
after
refrigerating the paste at 4 C for 2-3 hrs.
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The material could be stored in a paste form for about 12 hours at 4 C in an
air
tight container without hardening.
Example 8: Characteristics of a Synthetic Poorly Crystalline Apatitic Calcium
Phosphate
Material.
The crystalline content of the PCA material was determined by X-ray
diffraction
and I-R spectrometry.
Fig. 5a-d are the X-ray diffraction spectra of the reaction product between
DCPD
and the reactive amorphous calcium phosphate as described in Example 4. The
reaction
mixture was placed in a moist environment at 37 C and examined by X-ray
diffraction
spectrometry at different times. X-ray scan conditions were (a) copper anode,
(b) X
1.4540598 A, and (c) a scan range 20-35 at a step of 0.02 and step
interval of 2
seconds. Figure 6 shows the infrared spectra of dicalcium phosphate dihydrate
(a), the
activated ACP of the invention (b), and the PCA material of the present
invention (c).
Samples of Figs. 5a-5d were incubated for 0, 20 min, 75 min and 5 hours,
respectively. The samples were removed at the noted time and lyophilized to
preserve
chemical characteristics. Fig. 5a. taken at the start of the reaction,
represents a
combination. of peaks attributable to the starting ACP and dicalcium
diphosphate (see,
Fig. 4 for component XRD patterns). The sharp peaks at ca. 20.25 , 23.5 ,
29.5 ,
30.75 and 34.2 for crystalline dicalcium diphosphate are readily observed.
With
increase in reaction time, the sharp crystalline peaks subside and wide
(amorphous) peaks
appear centered at 26 , 28. 5 , 32.0 and 33 .0 . It is interesting to
note that there is no
significant change in the spectra after 75 minutes of reaction, indicating
that the
conversion reaction was essentially complete in little more than one hour. The
X-ray
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diffraction pattern of the PCA material of the invention (Fig. 5d) can be
compared to that
of naturally occurring bone, shown in Fig. 7. The two spectra are nearly
identical,
indicating the close biomimetry of the apatitic calcium phosphate of the
invention.
Examples 9-12: Characteristics of Injectable Paste for Formation of Synthetic
PCA
material from a Reactive, Amorphous Calcium Phosphate
These examples demonstrate the effect of fluid volume on the consistency and
reactivity of injectable paste to be used in the formation of a synthetic,
poorly crystalline
hydroxyapatite material. Each of the pastes were prepared as described in
Example 7,
above, and the consistency and rate of reaction at room temperature and 37 C
were
determined.. Observations are reported in Table 2.
Table 2
Formability, injectability and reactivity of one gram drug PCA material
prepared with variable
water volume
Example No. water volume formability injectability hardening time
(mL,) (min)
(4 ' C/RT/37' C)
9 0.7 - - -/_/-
crumbles
10 0. 8' +++ + > 60/ > 60/30
easily formed
paste
11 0.9' ++ ++ > 60/ > 60/30
toothpaste
12 1.0 + +++ >60/>60/30
liquid toothpaste
Under some circumstances (e.g., evaporation) these samples may dry out
somewhat over a period
of one hour at room temperature. In such cases, additional water may be added
to restore the
original consistency.
Example 13: Infrared Spectra of Precursor and Product Materials
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This example compares the infrared spectra of crystalline and amorphous
precursors produced according to the Examples and the final PCA material
produced by
reacting similar precursors. Fig. 7a presents the IR spectrum of brushite
(DCPD)
prepared as described in Example 4; Fig. 7b presents the spectrum of ACP after
heat
treatment, prepared as described in Example 1; and Fig. 7c is the IR spectrum
of the
PCA material prepared as described in Example 4.
Example 14: Implantation and Resorption of PCA Material in a Bony Site
The purpose of this study was to assay resorption and ossification of PCA
calcium
phosphate in a bony implant site. The method is also useful for testing the
resorption and
ossification properties of PCA calcium phosphate formulations and composites
of the
invention.
The test article used was a PCA calcium phosphate formulation prepared as
described in Example 4. The ACP and DCPD were mixed in the specified
proportions
and ground for 1 minute, 30 seconds in the SPEX grinder equipment.
Adult (> 5 month old) NZW male rabbits were held in quarantine and
acclimatized for a minimum of 10 days prior to the initiation of the study.
Animals were
individually housed in suspended stainless steel cages. Wood shavings were
used in
dropping pans under the cages. Prior to initiation of the study, animals were
assigned to
groups or treatments randomly and were identified by a numbered ear tattoo and
by a
corresponding cage card. All animals had single defects placed in one tibia.
Timepoints
for evaluations were 2, 4, and 8 weeks (2 animals at each timepoint). Surgery
was
performed under full anesthesia and aseptic surgical conditions.
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After obtaining adequate anesthesia (e.g., ketamine/xylazine to effect), using
aseptic technique, an incision was made over the lateral proximal tibia. The
soft tissue
was deflected away and the bone exposed. Using an approximately 5 mm trephine
in a
low speed dental handpiece with irrigation (0.9% physiologic saline) as
needed, a--5.5
mm diameter hole was cut through the cortical portion of the bone. The bony
disk was
dissected free from the cortex and the site was prepared for implantation. The
hydrated
precursor material in paste form was placed into the defect. Defects in
control animals
were left untreated. The soft tissues were then closed in layers. One sample
per animal
was prepared using this method.
Clinical observations of the animals' general health and well-being, with
special
regard to their ambulatory abilities, were made at least weekly. All animals
appeared to
be in good health. At the end of the study the animals were euthanized with an
overdose
of anesthetic and the implant site collected. Radiographs of the tibiae were
made at
scheduled intervals including after surgery and at the time of necropsy.
The implantation sites were fixed in formalin and stained with either
hematoxylin
and eosin, Masson's trichrome, or Von Kossa stained slides from decalcified
samples.
Undecalcified histological samples were also prepared and stained with light
green basic
fuschin. Slides were microscopically evaluated by a board certified veterinary
pathologist
(ACVP) with experience in laboratory animal pathology. Subjective observations
were
made of bone morphology, and presence or absence of organized bone and of
detectable
PCA calcium phosphate material was noted.
Histological results indicated some mineralization at 2 weeks. By 4-6 weeks,
animals receiving implants had normal trabecular bone at the implant site with
no
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evidence of remaining PCA calcium phosphate. The untreated controls had not
fully
healed in that they had less than full ingrowth and/or had non-cortical-type
bone. Figures
l0a and lOb are photomicrographs of untreated and treated tibia defects,
respectively, 2
weeks after surgery. As can be seen, bone to the right of the defect edge in
the untreated
sample (Fig. 9a) is thin trabecular bone; new bone to the right of the defect
edge in the
treated sample is thick trabecular bone.
Example 15: Implantation and Resorption of PCA Material in a Subcutaneous Site
This example demonstrates the resorption of the inventive PCA calcium
phosphate
when implanted subcutaneously into rats. It also demonstrates a useful
screening
procedure to test resorption characteristics of new formulations of bioceramic
implant
materials and composites.
Eighty male and eighty female Sprague-Dawley rats were each implanted with 4
ml (2-4 gm) of the inventive PCA (prepared according to Example 4) into the
dorsal
subcutis (> 10 x the amount considered maximal in humans on a per kg basis).
Control
animals were treated with an equal volume of saline. Operation procedures are
described
in Example 16. The rats were sacrificed according to the schedule presented
below in
Table 3; the implant site was examined as described in Example 16.
Table 3
Sacrifice Schedule
Sacrifice Timepoint PCA calcium phosphate implant
1 week 5 m/5 f
2 weeks 5 m/5 f
1 month 5 m/5 f
3 months 5 m/5 f
1 year 20 m/20 f
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Blood for clinical pathology analyses was collected via retroorbital sinus or
cardiac
puncture (all by the same method) while the animals were under CO2 anesthesia.
Blood
samples were collected from each group of animals prior to scheduled
sacrifice. Clinical
observations of the animals for general health and well-being were performed
at least
weekly until 3 months, and then monthly.
At 1 week PCA material was present at the implant site and was found
associated
with moderate to marked granulomas presumable associated with the resorption
process.
At week two a small amount of PCA material was still present at the implant
site and
associated granulomas were mild to moderate. By week four most tissue appeared
normal
with a few mild granulomas persisting at the implant site. At week twelve no
evidence of
the implant remained.
ExaWle 16: Implantation and Resorption of PCA Material in an Intramuscular
Site.
This example describes the preparation of PCA material implants that have
varied
in vivo resorption times as a result of varied grinding times. Individual dry
precursors,
ACP and DCPD were prepared as described in Example 4. Several different
formulations of DCPD and ACP were then prepared by i) grinding DCPD for 15
sec, 30
sec, 1 min, 2.5 min, or 5 min in a SPEX grinder; ii) combining the ground DCPD
1:1
with ACP; and iii) grinding the mixture for an additional 15 sec, 30 sec, 1
min, 2.5 min,
or 5 min, respectively. Total grinding times for the different preparations
were therefore
sec, 1 min, 2 min, 5 min, and 10 min.
The PCA calcium phosphate, sterilized in powder form by approximately 2.5
Mrad of gamma irradiation, was prepared as described in Example 4 by taking
the
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material in powder form and mixing with sterile water or saline and forming it
into
approximately 1 cm disks 2 mm thick and incubated for a minimum of 30 minutes
at 37
C. Disks were implanted into adult male New Zealand White Rabbits immediately
following fabrication.
Animals were assigned to dose groups which contained 3 males for a total of 15
animals. The implants were assigned to the rabbits randomly. 10-15 minutes
prior to the
surgery, the animal was premedicated with xylazine (10 mg/kg, i.m.). The
animal was
then given ketamine (50 mg/kg, i.m.). The dorsal surface of the animal was
clipped free
of hair and washed with a betadine surgical solution and alcohol. Before the
surgery the
animal was monitored to be sure that is was properly anesthetized. To do this,
pressure
was applied to the foot pad. When there was no response, the animal was
properly
anesthetized. Throughout the procedure, the animal was monitored for whisker
twitching
and the toe-pinch reflect, which indicated that the animal was not waking up.
Using aseptic technique and a scalpel blade, an incision 1-2 cm in length was
made in the skin over the m. longissimus lumborum (which lies along both sides
of the
spine). When the incision was made, the underlying fascia and muscle was also
cut to
allow the sample to pass into the muscle. The sample disk was placed directly
into the
muscle, being sure that the entire implant was embedded in the muscle. The
muscle was
closed with a single absorbable suture and the skin was stitched closed
subcutaneously.
Metal skin staples were used to close the external skin surface incision. Five
samples
were placed on each side in this manner. Each sample was placed at the end of
the
incision and they were approximately 1 cm apart from each other (see diagram).
The
samples were in the form of 7 mm by 2 mm disks weighing approximately 150 mg.
The
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animals were monitored and were given buprenorphine (0.02-0.05 mg/jg, s.q)
upon
awakening. The analgesic was administered 2 times per day for three days after
surgery.
The animals were radiographed immediately after the surgery and for every two
weeks thereafter. The radiographs were compared to track the resorption of the
materials. A standardized method was used for the radiographs to minimize any
variation
between timepoints.
After euthanasia, implant sites were first evaluated by gross examination. In
those
sites with visible implants, the implants appeared as grey to yellow solid
discs. In those
sites where the implant had been resorbed, areas of red to tan discoloration
of the muscle
were observed.
Muscle tissue, with the implants, was removed, being careful not to disturb
the
implants. The tissues and the identifying marks were placed into labeled jars
filled with
10% neutral buffered formalin. All implant sites were processed and evaluated
microscopically. Observations included focal fibrosis, focal granulomatous
inflanunation,
and appearance of the implant (in some cases). Fibrosis was primarily seen as
fibrocytes
and collagen. Animals with gross resorption had fibrosis and minimal to
moderate
granulomatous focal inflammation. Granulomatous inflammation was seen as focal
aggregates of macrophages and giant cells, often with intracytoplasmic
crystals, and
occasional heterophils and lymphocytes. Inflammation around the non-resorbed
implants
was primarily minimal to mild fibrosis and/or granulomatous inflammation, both
of which
are within the acceptable range for intramuscular implants.
At four weeks, the pellets made from PCA calcium phosphate implants that had
been prepared by grinding for 30 seconds, 1 minute, or 2 minutes were fully
resorbed.
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Those that had been prepared by grinding for 5 minutes or 10 minutes were not
fully
resorbed.
Example 17: Implantation and Resorption of PCA Material in a Bony Site
The purpose of this study was to assay resorption and ossification of the PCA
calcium phosphate of the invention in a bony site.
Mature (> 1 year) beagle dogs were employed for this study because of their
size
and historical use as a model for bone studies. The tibia of the dog is large
enough to
allow large (> 5 mm) defects to be created and studied without compromising
the ability
of the animal to ambulate without inducing fractures secondary to induction of
defects in
the bones.
Ten adult male and female beagle dogs (6.0-15.0 kg) received the same
treatment;
Defects were created in the lateral surface of the tibial crest cortex (8 mm
or 10 mm) in
each tibia. PCA calcium phosphate was placed in the defect in one tibia and
the other
tibia served as a control.
An incision was made over the proximal tibia. The soft tissue was deflected
away
and the bone was exposed. Using an 8 mm trephine in a low speed dental
handpiece with
irrigation (0.9% physiologic saline) as needed, the bony disk was dissected
free and the
site was prepaared for implantation. The inventive calcium phosphate material
(solid or
paste) was placed into the defect. The soft tissues were then closed in
layers. One to
three samples per animal were performed using this method. The animals were
allowed
to heal for scheduled periods of time.
Animals were assessed by clinical observations, radiographs, and microscopy of
the defect sites at 0, 2, 4, and 8 weeks. Specifically, tibia radiographs were
taken every
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2 weeks throughout the study. The radiographs were used to determine the
duration of
the study. Approximately at the end of every 2 weeks, 2 animals were
sacrificed and the
test sites were removed for histology. The implantation sites were prepared as
undecalcified and decalcified sections.
Two dogs were used as pilot animals and did not receive and PCA material. In
these pilot animals, some healing was observed radiographically at 2 weeks. By
6-8
weeks, the defect was completely healed. The size of dog defects was
determined to be
optimal at 1 cm. In the remaining 8 dogs, control defects healed within 6
weeks; treated
defects healed in 2 to 4 weeks. The quality of the bone in the control defects
was thin
trabecular bone; in the treated defects, the bone was thick trabecular to
cortical type
bone. Thus, the treated defects healed approximately 2 weeks faster than did
untreated
defects, and healed with better bone thickness.
Figure 11 shows a highly magnified (10x) photograph of canine trabecular bone
growth into a defect site treated with the PCA material of the invention 8
weeks after
surgery. The small arrows denote osteoblast - like cells lining the bone
spicules and are
indicative of enhanced cellular activity.
Figure 12 shows a photomicrograph of a canine cortical bone defect treated
with
the PCA material of the invention. The large arrows indicate one edge of the
defect.
The new bone growth is to the right of the defect; at 4 weeks after surgery,
this growth is
thick trabecular bone.
Example 18: Implantation and Resorption of PCA Material Implant in a Bony Site
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The purpose of this study was to assay resorption and ossification of the PCA
calcium phosphate of the invention, and to establish parameters for screening
test PCA
calcium phosphate materials.
Eighteen adult (> 3 month old) NZW male rabbits were used in these studies.
After obtaining adequate anesthesia (e.g., ketamine/xylazine to effect), using
aseptic
technique, an incision was made over the proximal tibia. The soft tissue was
deflected
away and the bone was exposed. Using an approximately 5 mm trephine in a low
speed
dental handpiece with irrigation (0.9% physiologic saline) as needed, the bony
disk was
dissected free and the site was prepared for implantation. The inventive PCA
calcium
phosphate material (solid, granules or paste) was placed into the defect. The
soft tissues
were then closed in layers.
Clinical observations of the animals general health and well-being, with
special
regard to ambulation, were performed weekly and in more detail at the time of
the bi-
weekly radiographs. Radiographs of the tibiae were made at scheduled intervals
including
after surgery and at the time of necropsy.
The implantation sites were prepared as hematoxylin & eosin, Masson's
trichrome
decalcified samples and as undecalcified slides.
Findings and clinical observations were associated with surgery and were not
associated with the PCA calcium phosphate implants. Postsurgical clinical
observations
were within the range of anticipated findings for surgery-related trauma.
Radiographs
were taken inunediately postsurgery and at each scheduled sacrifice timepoint.
Immediately after surgery, all bone defect sites were distinct; implants
appeared to
have the same radiodensity as bone. At 2 weeks postsurgery, control defects
had distinct
sites and implant sites were less distinct and blended into surrounding bone;
similar
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findings were observed at 4 weeks. At 7 weeks, all sites appeared similar with
increased
radiodensity. Grossly, defect sites at 2 weeks were visible clearly in control
and treated
animals. At 4 weeks and greater, the implant or control sites could not be
grossly
ascertained.
Radiographic findings indicated little change in the control animals until
week 7;
animals treated with inventive PCA material had increasing radiodensity in the
defect over
time. Defects in control animals had some new bone ingrowth, predominantly of
the thin
trabecular type, within 4-7 weeks. Defects in treated animals had bone
ingrowth as early
as 2 weeks and by 7 weeks were filled with new bone. Microscopic findings are
consistent with enhanced bone replacement with PCA calcium phosphate implants.
Taken
together, this study shows that 5 mm defects in rabbit tibia heal or have new
bone growth
in control animals by 7 weeks and in animals treated with the inventive PCA
material by
4 weeks. Also, this rabbit unicortical 5 mm critical sized defect model is
useful to
analyze test articles for there resorptive and ossificative properties.
Figure 13 shows photomicrographs of untreated (Fig. 13a) and treated (13b)
rabbit
tibia defects 4 weeks after surgery. The large arrow indicates the edge of the
defect. In
Fig. 13a, small arrows 100 denote an abundance of fibrous connective tissue on
the defect
site. The large arrowhead 102 points to new trabecular bone in the defect. In
Fig. 13b,
the two small arrows 104 demarcate the thick trabecular bone growth in the
defect site.
Example 19: Variation of Resorption Rates of Synthetic PCA Materials by
Varying
Particle Size
PCA precursor material is prepared according to Example 5. Two precursor
mixes are prepared, sample A corresponding to sample 6 and sample B to a
2:4:3:1 mix
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of samples 1,2,3,&4. Hydrated precursor pastes of the two samples are tested
in rodents
in the subcutaneous test of Example 15. Resorption is monitored at various
time points.
Example 20: Incorporation of a Biologically Active Agent into a PCA Material
Device
and Preservation of in vitro Stability
This example demonstrates the incorporation of a protein into a delivery
vehicle of
the present invention in a manner that preserves the protein's in vitro
stability.
Bovine pancreatic trypsin is prepared in phosphate buffered saline at a
concentration of 100 mg/ml. 0.8 ml of this solution is added to 1 g of a 1:1
mixture of
activated ACP and DCPD as described in Example 17, sample B. The mixture is
formed
into a ball and hardened in a moist environment at 37 C for 30 minutes. The
hardened
ball is then lyophilized overnight and subsequently it is ground by and with a
mortar and
pestle. The-powder formed this way is mixed with 1 ml of water and applied to
wells in
a casein assay plate. The clearance of the cloudy casein in a ring around the
well is
compared to the clearance observed in a well similarly loaded with a
lyophilized PCA
sample continuing heat inactivated trypsin.
Example 21: Incorporation of a Biologically Active Agent into a PCA Material
Device
and Preservation of in vivo Stability
This example demonstrates the incorporation of a protein into a delivery
vehicle of
the present invention in a manner that preserves the protein's in vivo
activity.
200 mg/ml Beta galactosidase (Worthington LS004093) is prepared in phosphate
buffered saline pH 7Ø 0.8 ml of this solution is added to 1 g of a 1:1
mixture of
activated ACP and DCPD (prepared as described in example 17, sample B.) and
mixed
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into a putty. The formable PCA is then prepared in a ball and implanted
subcutaneously -
in a rat. Two weeks later the PCA ball is removed, lyophilized and ground with
a mortar
and pestle. The powder is then assayed for beta galactosidase activity, for
example using
a liquid assay such as that described by Miller (Experiments in Molecular
Genetics, Cold
Spring Harbor Laboratory Press, Cold Spring Harbor, NY11972).
Example 22: Delivery of an Antibiotic
This example demonstrates use of the delivery vehicle of the present invention
to
deliver antibiotic in a dental application.
100 mg/ml gentamycin is prepared in phosphate buffered saline pH 7Ø 0.8 ml
of
this solution is added to 1 g of a 1:1 mixture of activated ACP and DCPD
(prepared as
described in Example 17, sample B.) and mixed into a putty. The formable PCA
is then
prepared in a ball and implanted subcutaneously in a rat. Two weeks later the
PCA ball
is removed, lyophilized and ground with a mortar and pestle. The powder is
then assayed
for bactericidal activity using a USP bacteriacidal/bacterialstasis zone of
inhibition test.
Example 23: Delivery of a Vaccine
This example demonstrates use of the delivery vehicle of the present invention
to
deliver a vaccine.
Keyhole limpet hemocyanin is prepared at a concentration of 0.5 mg/ml in
phosphate buffered saline pH 7Ø 0.8 ml of this solution is added to 1 g of a
1:1
mixture of activated ACP and DCPD (prepared as described in Example 17, sample
B.)
and mixed into a putty. The formable PCA is then prepared in a ball and
implanted
subcutaneously in a rat. The process is repeated on a monthly basis for four
months.
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Blood samples are taken on a regular basis and anti-Keyhole limpet hemocyanin
antibody
titers are determined by ELISA.
Example 24: Delivery of a Nucleic Acid
This example demonstrates use of the delivery vehicle of the present invention
for
intramuscular delivery of a nucleic acid for the purpose of cell transfection.
This method
may also be used to incorporate DNA into tissues other than muscle.
pUC19 plasmid DNA is prepared in EDTA TRIS pH 7.4 at 2 mg/ml. 0.8 ml of
this solution is added to 1 g of a 1:1 mixture of activated ACP and DCPD
(prepared as
described in example 17, sample B.) and mixed into a putty. The formable PCA
is then
prepared in a ball and implanted intramuscularly in a rat. After 4 weeks the
muscle at
the implant site is dissected and histologically stained for the presence of
the B
galactosidase gene product.
Example 25: Implantation and Resorption of PCA Material Device for Treatment
of
Parkinson's Disease.
This example demonstrates use of the delivery vehicle of the prevent invention
to
deliver a drug for the treatment of Parkinson's Disease.
Primates are made hemi-parkinsonian with MPTP and evaluated behaviorally as
described in Kordower et al., Cell Transplantation 14:155-171, 1995.
200 mg/ml GDNF is prepared in phosphate buffered saline pH 7Ø 0.8 ml of this
solution is added to 1 g of a 1:1 mixture of activated ACP and DCPD (prepared
as
described in Example 17, sample B.) and mixed into a putty. The hydrated PCA
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precursor is then shaped into 3 cylinders each approximately 1 mm x 1 cm and
hardened
in a moist environment at 37 C.
The cylinders are then placed in the lateral ventricles on the lesioned side
of the
experimental animals and the primates are continued to be behaviorally
evaluated. After
two months the animals are sacrificed and neurons of the substantia nigra and
striatum are
analyzed for tyrosine hydroxylase activity.
Example 26: Pre-hardened Implant: Augmentation and Resorption in the Canine
Mandibular Onlay Model
The purpose of this study was to evaluate resorption, ossification and
biocompatibility of two formulations of the inventive PCA calcium phosphate in
canine
mandibular sites. Prehardened PCA calcium phosphate was implanted in a canine
mandibular onlay model which additionally may be used as an augmentation
model.
The test article was PCA calcium phosphate in two formulations, corresponding
to
Types 2 and 10 described in Example 16. The PCA calcium phosphate was pre-
hardened
in a moist environment at approx. 40 C immediately prior to implantation.
The control
implants were 3 mm x 4 mm cylinders of silicone and porous hydroxyapatite,
respectively.
Two adult female hound-type dogs (20 to 25 kg) were used in the study. Both
dogs received two control implants (1 of each) on the right side of the
mandible and one
each of the Type 2 and Type 10 PCA calcium phosphate formulations on the left
(opposite) side.
Implantation was performed under full anesthesia and aseptic surgical
conditions.
The animals were premedicated with tranquilizers and atropine-type agents and
induced
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with barbiturates. The animal's vital signs (temperature, heart rate,
respiratory rate) were
monitored before and throughout the procedure. The animals were tested for
proper
anesthetic depth by toe pinch and corneal stimulus. After obtaining adequate
anesthesia,
using aseptic technique, an incision was made in the skin over the midlateral
ventral
surface of the mandible and proximal neck (over the mandible lower edge). The
soft
tissue was deflected away and the bone was exposed. The periosteum over the
outer
mandibular surface was elevated and the bone surface was roughened with a burr
or drill
until it was rough and bloody in a shape to accept the cylindrical implants.
The control
articles and pre-hardened PCA calcium phosphate were placed into the defects.
Two
samples per animal per side were onlaid onto each outer mandible surface using
this
method (two experimental PCA calcium phosphate samples and two controls). The
samples were placed about 1 cm to insure that they do not appose each other.
The
periosteum was closed first using 3.0 vicryl. The soft tissues were then
closed in layers
with 3-0 vicryl absorbable suture. The skin was closed with simple interrupted
sutures of
5-0 nylon. The animals were allowed to heal for scheduled periods of time. One
dog
was sacrificed at 3 weeks and the other at 3 months and the test sites were
removed for
histology. All animals were euthanized and identifying marks were collected.
The implantation sites were prepared as undecalcified sections. Sections were
evaluated for biointegration, biodegradation, and biocompatibility.
The results were as follows: At all time points excellent biocompatibility was
observed. No giant cells and minimal macrophage were observed. There was only
minimal reaction layer of only a few cells thickness at the base of the PCA
calcium
phosphate implants. This is significantly better than was observed for either
of the
controls.
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At three weeks, the majority of the Type 2 material was resorbed.
At twelve weeks, the Type 2 was completely resorbed to the surface of the
original bone.
Additionally the bone in the socket was not fully differentiated.
The Type 10 samples demonstrated osseointegration with new bone ingrowth and
cell migration into the implant. The implant itself was approximately 10 %
resorbed after
twelve weeks.
The silicon control implant, which is not resorbable, displayed a mild to
moderate
foreign body reaction. Voids were unfilled at three weeks, but by twelve weeks
were
filled with fibrous tissue. The hydroxyapatite control implant showed no signs
of
resorption or osseointegration within the first twelve weeks.
This experiment confitms the excellent biocompatibility of the inventive PCA
calcium phosphate. Additionally, a difference in resorption time between the
two PCA
formulations was observed, with a prolonged resorption time course for the
sample in
which the precursors were mixed/ground for a longer period of time (Type B).
The results also point out the slower resorption and ossification properties
observed in the non-load bearing mandible implant site as compared to rapidly
ossifying
load bearing applications of Examples 14, 17 and 18.
Example 27: Ectopic Bone Production
This example describes the production of ectopic bone in an animal model using
an inventive cell seeded PCA material.
The PCA material is prepared and implanted either subcutaneously or
imtramuscularly as described examples 15 and 16, except that the material is
not pre-
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hardened, the hydration medium used is 0.8 ml/gm phosphate buffered saline pH
7.4, and
the material is seeded with cells as described below. In some instances 0.2
mg/mi of
BMP 7 is included in the hydration medium.
Prior to implantation, the 1 g sample of hydrated PCA is inoculated using a
sycinge with approximately 50 l of the subject's bone marrow harvested
previously with
a biopsy needle. The hydrated precursor is then implanted. Enough subjects are
used to
allow recovery of the PCA on a biweekly basis to study ectopic bone
production.
Example 28: Production of Cartilage in vivo with Autologous Cell Seeding
This example describes the production of cartilage on the surface of a bone
from
an inventive'PCA material composition seeded with autologous cartilage-
producing cells.
In a number of instances involving dogs and rabbits, unexpected formation of
cartilage was observed when bone that had been treated with PCA material was
histologically examined. Figure 18 is a photomicrograph of a radial bone from
a NZW
rabbit, stained with hematoxylin and eosin. A small mound of PCA material had
been
inadvertently applied to a region of healthy bone, and the formation of
cartilage is clearly
observed in the center of the mound of PCA. Native bone is designated as 2 and
cartilagenous region is indicated at 1.
Example 29: Production of Cartilage in vitro
This example describes the in vitro production of cartilage from a cell-seeded
PCA
material composition of the present invention.
Human chondrocytes are prepared and cartilage production determined according
to Goldring (Methods in Molecular Medicine Human Cell Culture Protocols,
Edited by
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Jones, Human Press, pp. 217-232, 1996, incorporated herein by reference); rat
cell line
CFK2 is maintained according to Bernier et al. (1993 J. Bone Miner. Res. 8:
475, 1993);
and articular and intervertebral chondrocytes are prepared according to Rivard
et . al.
(Fifth World Biomaterials Congress, pg. 291, 1996). All procedures are
performed
asceptically under sterile conditions.
Sterile PCA hydrated precursor is prepared according to example 5, sample 5.
Hydration medium is 2 X HBSS (50 mM HEPES, 10 mM KCI, 280 mM NaC1 and 12
mM glucose pH 7.5). The hydrated precursor is formed into two slabs, each of
which is
about 1 mm thick and approximately 1 cm square. A small indentation is
prepared in the
first slab, and about 25,000 cells in approximately 5 l of growth medium
containing
10% FCS are placed within the well. The second slab is placed on top of the
first slab,
and edges of the two slabs are gently pinched together. The resultant
composition is
placed in a petri dish so that it is submerged in growth medium containing 10%
FCS.
The petri dish is placed in an incubator at 37 C in 5% CO2. The medium is
changed
every three to four days. Enough replicates are prepared to analyze a sample
on a weekly
basis for the formation of cartilage.
Example 30: Ectopic Cartilage Formation
This example describes the production of ectopic cartilage in an animal model
using an inventive cell-seeded PCA material composition.
The PCA material is prepared and implanted either subcutaneously or
intramuscularly into rabbits as described in examples 15 and 16, except that
the material
is not pre-hardened, the hydration medium used is 0.8 ml/gm phosphate buffered
saline
pH 7.4, and the PCA material is seeded with cells as described below. In some
instances, 0.2 mg/ml of type 1 collagen is included in the hydration medium.
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Prior to implantation, the 1 g sample of hydrated PCA is inoculated with
approximately 100 1 of enzymatically-isolated autologous knee joint cartilage
chondrocytes. Preferably, the chondrocytes are delivered into the PCA material
using a
syringe. The cell-seeded hydrated precursor is implanted. Enough subjects are
used to
allow recovery of the PCA on a biweekly basis to study ectopic cartilage
production.
Example 31: In vivo Cartilage Repair
This example describes the production of ectopic cartilage in an animal model
using an inventive cell-seeded PCA material composition.
A PCA material hydrated precursor is prepared and implanted into dog knee
joints
in which cartilage has been surgically removed. The hydration medium used is
0.8 ml/gm
phosphate buffered saline pH 7.4, and the hydrated precursor is seeded with
cells as
described below. In some instances 0.2 mg/ml of type 1 collagen is included in
the
hydration medium.
Prior to implantation, the 1 g sample of hydrated precursor material is
inoculated
with approximately 200 l of enzymatically isolated autologous knee joint
cartilage
chondrocytes. The chondrocytes are preferably delivered by syringe. The cell-
seeded
hydrated precursor is implanted. Enough subjects are used to allow recovery of
the PCA
on a biweekly basis to study joint cartilage production.
Example 32: Cell Encapsulation Matrix
This example describes the use of inventive PCA matrices for encapsulated cell
therapy. Encapsulation devices are prepared according to known methods (see
Aebischer
et al., U.S. Patent No. 4,892,538; Sefton et al., U.S. Patent No. 4,353,888,
Winn et al.
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Experimental Neurology 140:126 (1996), each of which is incorporated herein by
reference).
Devices are loaded with hydrated precursor paste in the presence of 15,000
fibroblasts and sealed. Devices are maintained in vitro or implanted into
animal
recipients. Devices are explanted periodically and checked with trypan blue
for cell
viability.
Example 33: In vivo Augmentation with a PCA/HA Composite
This Example demonstrates the use of a relatively slowly resorbing PCA
material
in a PCA/HA composite to produce a long lasting, shape-retaining skeletal
augmentation.
PCA/HA composites are prepared by mixing particulate HA (grain size < 200
m) with the inventive hydrated precursor putty described in example 5, sample
5, in a
ratio ranging from 0.05 to 30 % wt/vol. The granular putty produced by this
mixing is
shaped in a form suitable for implantation. The granular putty is then
hardened at 37 C.
The implant site is prepared by dissecting away a few millimeters of the
cortical
bone, including the periosteum. If possible, the periosteum is peeled back
from the
cortical bone surface at the implant site, but is left attached. The material
and blood from
the dissected bone is retained and mixed with fresh PCA material paste (i.e.,
hydrated
precursor) in about a 1:3 vol/vol ratio, and is set aside. Fresh PCA material
paste is used
as a cement to affix the implant to exposed cortical bone surface. Additional
PCA
material paste is applied as needed to ensure adherence of the implant. The
retained
PCA/tissue material mix is then used as a seeding source for the implant and
is applied to
as much of the implant surface as is possible. The periosteum is then drawn
back over
the implant as much as possible.
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Example 34: Production of PCA Calcium Phosphate Using an ACP and Participating
Promoters.
This.example demonstrates the hardening properties and PCA calcium phosphate
formation from ACP using a number of different participating promoters. Highly
reactive ACP was prepared according to Example 1.
The nanocrystalline hydroxyapatite of samples 1-1, 1-2 and 1-3 were prepared
without inhibitors of crystallization as follows: 218 g of disodium hydrogen
orthophosphate (Na2HPO4.12H2O) were dissolved in 1200 mL of solution of
distilled
water. For carbonated PCA calcium phosphate of samples 1-1 and 1-2, 80 g of
NaHCO3 were also added to this solution. 70 g of calcium nitrate
[Ca(NO3)z.4H20]
were dissolved in 500 mL of distilled water. The calcium solution was quickly
poured
into the phosphate solution at room temperature with constant stirring.
Precipitation
was immediate and substantially complete. The pH of the precipitate was
adjusted to
7.4 by the addition of sodium hydroxide solution in order to avoid the
formation of
acidic calcium phosphates. The precipitate was immediately separated from the
solution
by filtration through a Buchner filter (with a total surface about 0.1 sq.m),
and was
washed by about 3 liters of distilled water. A gel cake of low crystallinity
calcium
phosphate was obtained on the filter paper. A portion of the gel cake was
immediately
lyophilized for samples 1-2 and 1-3.
For sample 1-1 the gel cake was treated as follows: After filtration and
washing,
an appropriate amount of distilled water (5 to 80 weight %) was added to the
gel
precipitate. The gel was homogenized by whipping energetically for a few
minutes. It
was then cast into polytetrafluoroethylene (PTFE) molds (diameter 60 mm;
height 2
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mm), and sonicated for a few minutes in order to release the air bubbles
trapped in the
gel.
The molds were dried in a chamber at controlled temperature (5 to 37 C) and
humidity (10 to 95% RH). The samples shrank slowly on drying and released most
of
their water. The rate of drying and the shrinkage of the samples depended on
the
initial water content. The material hardened on drying and became glassy. It
contained
about 10% of residual water.
The remaining hydroxyapatites and calcium sources were used as is from
commercial sources.
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Table 4
ACP Conversion Using Participating Promoters
participating promoter incubation extent of PCA" PCA' by
sample
at 37 C hardening by FTIR XRD
carbonated nanocrystalline 30 min starting to set
1-1
hydroxyapatite, air dried 2 hrs hard yes ND
1-2 carbonated nanocrystalline 30 min hard
hydroxyapatite, lyophilized 2 hrs hard yes yes
1-3 non-carbonated nanocrystalline 30 min starting to set
hydroxyapatite, lyophilized 2 hrs hard yes ND
1-4 Aldrich hydroxyapatite 30 min hard yes yes
grain size < 15-30 m
1-5 Clarkson hydroxyapatite 30 min starting to set yes ND
grain size> 250 m
1-6 Monetite - non calcinated 30 min soft yes ND
grain size 15 hrs starting to set
1-7 CaCO3 30 min starting to set yes ND
hrs
1-8 Ca(OH). 30 min soft yes and ND
1 5hrs starting to set Ca(OH)2
1-9 Ca(CH3COO)Z 30 min soft yes ND
15 hrs soft
PCA = poorly crye apatitic c cium p osp ate
15 ND = analysis not done
ACP was mixed with the specific promoter at a ratio (wt/wt) of about 50:50
(see
Table 1) for 5 minutes in a SPEX laboratory mill. Approximately 0.8 mL H20/g
dry
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powders were added to the dry precursor mixture and mixed to a paste. The
mixture
was then shaped into a ball, wrapped in moist tissue paper and heated to 37 C
for at
least 30 minutes. After 30 minutes and at various time points thereafter the
paste was
monitored for hardness. Figures 15 and 16 are representative XRD from
reactions 1-2
and 1-4. The use of two different grain size hydroxyapatites as participating
promoters
yielded similar results as with different grain size DCPDs (see Example 5)
That is, the
larger grain size hydroxyapatite hardened more slowly and less completely than
the
smaller grain size hydroxyapatite.
Example 35: Use of a Neutreal Apaptitic Calcuim Phosphate Promote
This example demonstrates the use of a neutral apatitic calcium phosphate as a
promoter for the conversion of ACP to the inventive PCA calcium phosphate to
promote bone growth in vivo. Stoichiometric hydroxyapatite is mixed with
reactive
ACP as described in Example 34-37. Hydrated precursor paste is applied to
animal
subjects as described in Examples 14, 15 or 16. Bone healing and
biocompatibility is
monitored as described at the time points indicated.
Example 36: PCA Material Production using Promotes
This example demonstrates the production of PCA calcium phosphate from ACP
using a number of different passive promoters.
Highly reactive ACP was prepared according to Example 5. ACP was mixed
with the specific promoter at a ratio (wt/wt) of about 5:1 or 1:1 (see Table
2) for 5
minutes in a SPEX laboratory mill. Water (0.75 - 0.85 mL) was added and mixed
to
form a putty. The mixture was then formed into a ball, wrapped in moist tissue
paper
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and heated to 37 C for at least 30 minutes. After 30 minutes and at various
time
points thereafter the paste was monitored for hardness. Figure 17 is a
representative
XRD from sample 2-4 employing an alumina promoter. In this figure the alumina
peaks can be seen superimposed over the standard PCA calcium phosphate
profile.
Table 5
ACP Conversion Using Passive Promoters
Passive
study # Promoter Incubation Extent of PCA' by PCA' by
(ACP:promoter) time at 37 C Hardening FTIR XRD
2-1 SiOZ (5:1) 30 min soft yes yes
3 hrs very hard
2-2 Mica (5:1) 30 min soft yes yes
12 hrs very hard
2-3 A1,03 (1:1) 30 min soft yes yes
12 hrs very hard
2-4 A1T03 (5:1) 30 min soft yes yes
12 hrs very hard
= PCA = poorly crystalline apatitic caicium phosphate
Example 37: Reaction Profile
This.example demonstrates the use of a scanning differential calorimeter (DSC)
to monitor temperature sensitivity and the net endothermic nature of a
preferred
embodiment reaction employing activated ACP and DCPD precursors.
The dry precursor mixture containing equal weights of ACP and DCPD was
prepared by mixing in a SPEX 850 laboratory mill with a SPEX 8505 alumina
ceramic
grinding chamber, ACP and DCPD precursors as described in Example 4, mixing
proceeded for 2 min. Preparation of the hydrated prcursor was accomplished by
adding
from 0.7 - 1.5 ml of water per gram of mixed dry precursors. Water (0.05 mL),
prechilled to approximately 4 C, was added to 47.27 mg of the dry precursor
mixture
and immediately placed into the calorimeter. The DSC (Perkin Elmer 7 series
thermal
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analysis system) was set to a starting temperature of 0 C with a scan rate of
5 C/min.
The results are shown in Figure 16. The plot represents a monitoring of the
first 7
minutes of reactivity and shows essentially no heat flow between 0.0 C and
approximately 20 C, at which point onset of endothermic heat flow occurs.
The heat
flow properties indicate that at 37 C the reaction is essentially
endothermic, and under
the conditions used, the reaction occurs only very slowly if at all at
temperatures below
about 20 C. Thus, the net reactivity in the system, that is, the sum of
endothermic
and exothermic heat flow of the system, is endothermic.
Example 38: Absence of Hardening in Certain Compositions
This example describes the conversion of ACP to PCA calcium phosphate in the
absence of a promoter and demonstrates the failure of the newly formed PCA
calcium
phosphate to harden. Likewise, promoter DCPD fails to harden or convert on its
own.
DCPD and a variety of ACPs and other calcium phosphates were mixed with
water and tested for their ability to harden at 37 ' C. Table 6 summarizes
these results,
as well as identification of the reaction products, if any, following the test
period.
Under no circumstances was hardening observed up to 3 days. It was concluded
that
while conversion of ACP to PCA calcium phosphate may occur, the presence of a
promoter is desired to achieve setting and hardening
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Table 6
ACP conversion in the absence of a promoter
ACP HZO 'Incubation Hardening FTTR XRD
(g)
ACP (Example 5) 0.8 30 min soft ACP ACP
12 hrs soft PCA' PCA'
DCPD (Example 8) 0.7 30 min soft DCPD ND
38-53 m 12 hrs soft DCPD
ACP (Example 7) 1.5 30 min soft PCA' ND
not heat activated 12 hrs soft HA
ACP (Example 5) 1.5 30 min soft ACP ND
non-carbonated
ACP (Example 6) 1.5 30 min soft ACP ND
not heat activated
ACP (Example 5) 1.5 30 min soft PCA' ND
non-carbonated; heat
activated
PCA poorly crystalline apatitic calcium phosphate
ND = analysis not done
Example 39: Different Hydrating Agents Effects on Hardening and Final Product.
A hydrated precursor (ACP and DCPD) was prepared as described in Examples
4, 5 or 37 or 10, with the exception that a variety of hydration media were
used.
Samples were then tested for hardness and completeness of reaction at various
time
points. In all cases, 1 g of the mixed precursors were hydrated with 0.75 -
1.0 mL of
hydration medium to produce a paste. Table 7 summarizes the results and
demonstrates
that a variety of aqueous based liquids, and in particularly physiologically
acceptable
media, may be used in the preparation of PCA calcium phosphate.
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Table 7
Effect of Hydrating Agents
Hydration Medium Incubation Time Hardening
Tris 30 min hard
0.9M NaCI 30 min hard
MEM 30 min hard
MOPS 30 min hard
HEPES 30 min hard
BUFFERALL 30 min hard
PBS 30 min hard
Example 40: Analysis of Hardening
The porosity of a hardened sample of PCA calcium phosphate prepared
according to Example 5 was determined.
A hardened sample of PCA calcium phosphate (1 g) was weighed immediately
after removal from the moist incubator, and then air dried at room temperature
for 12
hrs. The dried sample was carefully weighed and then the volume was
calculated. The
sample was placed into a 20 mL sample of water. After 1 minute the approximate
displacement volume was noted. The dried sample was found to absorb up to 50 -
60 %
of its dry weight in H20. These results are interpreted to mean that the
sample is up to
50 -60 % porous. Density was approximated at 1.65 g/cm'.
Example 41: Use of Resorbable Polymer to Promote Conversion
This example demonstrates the use of a resorbable polymer to promote the
conversion of ACP to PCA calcium phosphate.
Granular PLLA is prepared and sieved to a size of 100 m. The powder thus
obtained is mixed with the ACP (5:1 ACP:PLLA) of Example 37 and ground for 5
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minutes in a SPEX laboratory mill. Water is added to 1 g of the mixture to
form a
workable paste. The paste is shaped into a ball and is heated to 37 C in a
moist
environment for 1 hour. The hardened sample is analyzed using FTIR and XRD.
Example 42: Sub-Ambient Hardening Characteristics
This example investigates the hardening characteristics of the hydrated
precursor
at sub-ambient temperatures.
Hydrated precursor was prepared with water as described in Example 37 and
then tightly sealed to avoid evaporative loss either in parafilm or in an
aluminum tube.
The samples were then held for up to 1 hr, 24 hrs and 6 days. At the indicated
time
points, the hydrated sample was removed from refrigeration placed in a moist
environment at 37 C. In all instances the samples hardened within 30
minutes.
Example 43: Room Temperature Hardening
This example demonstrates the effect of maintaining the hydrated precursor
uncovered at room temperature.
The dry precursor was prepared as described in Example 6 except C. The dry
precursor was mixed with the indicated amount of water and tested for
hardening and
injectability through a 16 gauge needle after standing uncovered at room
temperature for
various time periods. The results are reported in Table 8.
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Table 8
Paste Injectability after Standing at Room Temperature.
sample water mixing standing room injecta i ity ar ening;
wt (g) added time (s) time temp. for 16 30
(mL) (min) ( C) gauge min/37 C
needle
1 0.8 20 10 25 v. goo v. goo
0.8 20 20 24 v.good
v. goo
1 0.8 20 30 25 v. goo v. goo
1 0.8 20 40 25 good v.good
0.8 20 50 24 poor v.good
5 4.2 40 10 24 v. goo v.good
5 4.2 40 20 25 v. goo v. goo
5 4.2 40 30 25 good v. goo
5 4.2 40 40 25 poor v. good
These results demonstrate that a one gram sample may be stable as an
injectable
paste at ambient conditions for up to 45 minutes and that a 5 gram sample may
be
stable as an injectable paste for up to 30 minutes at ambient conditions (in
air, 25 C).
Example 44: Compressing Precursors Using Hydraulic Pess.
This example illustrates the method of preparing a pellet with a hydraulic
press.
A Carver Laboratory Press is used. A specific amount of powder is measured by
weight. The powder is then placed into the die set mold. The height or
thickness is
determined in part by the amount of material used in the mold. Once the
material is in
the die set, the mold is placed onto the hydraulic press. A desired load is
set on the
press. The material is then compressed for a specific amount of time. After
the time
has elapsed, the resulting pellet is expelled from the die set into a holding
container.
A 0.5g sample, ID = AB coml, from lot AB971002 was compressed at 500 psi
(pounds per square inch) for 5 minutes in the Carver Laboratory Press. The
physical
aspects of the resulting pellet were diameter= 13mm, height= 3mm, and the
density
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was 1.27g/cm3. The mechanical strength was described as hard and capable of
being
broken by hand. After FTIR analysis, the pellet was 70% PCA in wet tissue, 90%
PCA
in 20m1 distilled water, and 100% PCA in carbonated buffered solution (C03 -2
0.2mol). A second sample of 0.5g, ID= ABcom2, from lot AB971002 was compressed
at 4700 psi for 5 minutes in the Carver Laboratory Press. The pellet had the
following
results: diameter =13mm, height = 2mm, and the density is 1.99 g/cm3. The
mechanical
strength was described as very hard and capable of being broken by hand. When
the
pellet was incubated at 37C for 60 hours and analyzed through FTIR analysis,
the
following results were found: 60% PCA in wet tissue, 60% PCA in 20m1 distilled
water, and 60%PCA in carbonated buffered solution (C03 -2 0.2mol).
Example 45: Compressing Precursors Using Hand-held Press.
This example demonstrates the method of preparing a pellet with a hand-held
press.
A Perkin Elmer Quick Press is used. Pellets 7mm in diameter are made using
the selected die sets in conjunction with the Quick Press. Other die sets of
various
diameters can also be used depending on the desired measurements. The surface
of the
pellet can be flat or rounded, depending on the shape of the mold. The sample
is
loaded into the selected die mold. As the amount of sample increases, the
thickness of
the pellet also increases. Next, a reference position is selected from the
various manual
positions set on the top of the Quick Press. The die set is placed in position
in the
Quick Press. A steady pressure is applied to the handle of the Quick Press for
a
selected amount of time. Once the time has expired, the pellet is removed from
the
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mold by removing the bottom cap from the die set and applying pressure to the
top die
in order to expel the pellet from the die set.
A 0.08g sample, ID: AB com3, of AB from lot AB971002 was measured into the
7mm diameter die set. The Quick Press manual position was set at 20 and
compressed
for 1 minute. The resulting pellet had a diameter of 7mm and a height of
1.5mm; the
density was 1.39 g/cm3 . A second sample, ID: AB com4, of .1g of AB from lot
AB971002 was measured into the 7mm diameter die set. The manual position was
set at
20 and compressed for 30 seconds in the Quick Press. A resulting pellet was
formed
with a diameter of 7.0mm and height of 2.0mm; the density was 1.23g/cm3
Example 46: Behavior of PCA Pellets with Different Media.
This example describes the behavior of PCA calcium phosphate pellets in
different medias.
The four kinds of media chosen were: (-MEM (Minimum Essential Medium);
TBS (Tris Bovine Serum: 50mM of Tris + 150mM of NaCI); (-MEM + FBS (Fetal
Bovine Serum 10%); and Complete Media (immersion for 2h in TBS at 37C and
subsequent immersion into the (-MEM + FBS).
A 0.3g sample of mixed precursors ACP and DCPD was compressed for one
minute at 7 tons using the Carver Laboratory Press. The resulting pellet (a)
had a
diameter of 12mm and a height of 1mm. The pellet was put into 10m1 of
distilled water
at 37 C for 30 minutes. After incubation, the pellet was put in the 6m1 of
different
media at 37 C for 24 and 48 hours.
A second lg sample of mixed precursors ACP and DCPD was combined with
0.8ml of distilled water. The mixture was rolled into a ball and dropped into
lOml
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distilled water at 37 C for 30 minutes. The ball was then ground using a
mortar and
pestle to obtain a fine powder. The powder was pressed for one minute at 7
tons using
a Carver Laboratory Press. The resulting pellet (b) had a diameter of 12mm and
a
height of 1mm. The pellet was then put into the different media at 37C for 24
and 48
hours.
The pH of the solution of media was measured (at 25(C) at different times of
0,
24, and 48 hours after incubation at 37 C. The results of this study are
displayed in
Table 9.
Table 9. pH of Solution
Sample ca-MEM TBS a-MEM+FBS Complete
Preparation Oh 24h 48h Oh 24h 48h Oh 24h 48h Oh 24h 48h
Fa 7.6 8.1 7.9 7.5 7.0 6.8 7.5 7.7 8.2 7.6 7.9 7.9
b 7.3 7.3 7.1 7.3 6.5 6.0 7.4 7.5 7.5 7.5 7.5 7.3
Example 47: Reacting Precursors, Lyopholizing, Crumbling, Compressing.
This example illustrates how a pellet is formed from PCA calcium phosphate
paste.
PCA is made using ACP and DCPD, as the promoter. Saline is used as the
biologically suitable aqueous medium. The prepared PCA paste is then lyophol
hardened in vitro at 37 C and subsequently lyopholized. The hardened PCA
material
is then crumbled by hand. Once crumbled, the PCA material is formed into a
pellet by
methods described in examples 34 and 35.
Examl2le 48: Shaping, Hardening, Lyopholizing Without Grinding.
This example shows how a pellet is formed from PCA calcium phosphate paste.
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ACP and DCPD are selected as the precursors. An appropriate amount of Saline -
is used to make a PCA paste. The PCA paste is shaped into the desired form. It
is
then incubated at 37 C in vitro for 30 minutes. The hardened object is then
lyopholized.
Example 49: In Vivo Experiments Comparing the Methods.
This example compares the methods of producing the pellets through in vivo
experimentation.
Pellets are made according to Example 32. Two pellets are implanted into a dog
femur. The animals are sacrificed and the implantation sites are analyzed for
remaining
residual material at time points of 3, 4 and 6 weeks. At each time point,
decalcified and
undecalcified slides of the implantation site are prepared and stained. These
slides are
histomorphometrically analyzed to determine the similarity of the prepared
pellets to
that of PCA calcium phosphate paste.
Example 50:. Incorporation of a Filler or Binder.
This example demonstrates the use of a filler to study plastic flow, with
particular interest in the effect of tensile strength in the pellet.
A compressible sugar is used as a filler in conjunction with pellet
production.
The sugar is mixed with the precursors ACP and DCPD in a ratio of 1:1:1 before
compression. The pellet is produced according to example 1 with modifications
in the
duration of the total compression cycle and the duration of the maximum
compressive
force. The effectiveness of the sugar filler is measured by comparing the
tensile strength
of the pellets. The equation used to compute tensile strength is:
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vo = 2F/Hdt,
where Qo is the tensile strength, F is the force needed to cleave the tablet,
d is the
diameter of the pellet, and t is the tablet thickness or height.
Example 51: Delivery of a Vaccine in a Pellet.
This example explains how the pellet is used as a delivery vehicle for a
vaccine.
Keyhole limpet hemocyanin is prepared at a concentration of 0.5 mg/ml in
phosphate buffered saline pH 7Ø 0.8 ml of this solution is added to 1 g of a
1:1
mixture of activated ACP and DCPD and mixed into a putty. The prepared PCA
putty is then lyopholized. The dry material is milled for 10 minutes into a
powder
using a SPEX 8510 laboratory mill with a SPEX 8505 alumina ceramic grinding
chamber. The powdered PCA is then prepared in a pellet as described in Example
32.
A pellet formed by Example 32 is implanted subcutaneously in a rat. The
process is
repeated on a monthly basis for four months. Blood samples are taken on a
regular
basis and anti-Keyhole limpet hemocyanin antibody titers are determined by
ELISA.
Example 52. Canine anterior lumbar interbody fusion. This example describes
the use of PCA calcium phosphate in the fusion of canine spinal vertebrae.
Animals were anesthetized as described in Example 26, positioned in the right
lateral decubitus position, shaved from anterior to posterior midline,
extending form mid
thorax to the pelvis. Following sterile prep and drape, a standard left
retroperitoneal
approach to the anterior lumbar spine was performed, with exposure of the L3-
L6
vertebrae. The segmental vessels overlying LA and L5 were ligated and divided,
allowing
anterolateral exposure of the L3-4, L4-5 and L5-6 discs. Anterior discectomies
were
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performed at each level with the endplate prepared parallel and to bleeding
subchondral
bone using a parallel-paired-bladed oscillating saw (Aesculap). Following
discectomy, a
cylindrical titanium cage containing either PCA calcium phosphate or
autologous bone or
an unfilled cage was inserted into each disc space. Autogenous iliac crest
bone graft was
harvested from the left anterior iliac crest through a separate incision just
prior to its
packing into the cage and insertion into the disc space. After all three cages
were
inserted, internal fixation was applied using 4.5 mm vertebral body screws and
a 6 mm
diameter longitudinal rod from L3 to L6. Closure of the abdominal wound and
iliac crest
graft site was then done in layers using absorbable sutures and skin staples.
Dogs are sacrificed at two and twelve weeks and the histology of undecalcified
sections are examined for evidence of new bone growth and vertebral fusion.
Upon
visual inspection on explant, the spinal cords using the PCA calcium phosphate
of the
invention appeared fused.
Example 53: Bone Healing in the Presence of PCA Material
The purpose of this study was to examine bone healing in the presence of the
invented PCA material.
For this study, 30 adult NZW rabbits were used. Tap water and pellets of
certified
rabbit chow were available ad libitum throughout the course of the study.
Surgical
procedures were performed under full anesthesia and aseptic conditions.
Cefazolin was
then administered (22 mg/kg) 30 minutes before the surgery. The anesthesia
consisted of
10 ml (100 mg/ml) ketamine, 1 ml (100 mg/ml) xylazine, and 5 ml of 0.9%
physiologic
saline (87.5 mg/kg ketamine, 8.75 mg/kg xylazine). The anesthetic cocktail was
given at
a dose level of 1.4 ml/kg i.m. The animaUEs hind limb was then clipped free of
hair, and
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washed with a Betadine surgical solution and alcohol. Before the surgery the
animal was
monitored to be sure that it was properly anesthetized. To do this, pressure
was applied to
the foot pad. Once the animal was no longer responsive, further anesthesia
ceased.
Throughout the procedure the animal was monitored for whisker twitching, which
would
indicated revival of the animal. Using an aseptic technique, an incision was
made over the
proximal tibia. The soft tissue was deflected away and the bone was exposed.
An 8 mm
trephine dental handpiece at low speed was used for irrigation (0.9%
physiologic saline)
as needed. The bony disc was dissected free, and then the site was prepared
for
implantation. The PCA material was then placed into the defect. The soft
tissues were
closed in layers with 3-0 DexonTM suture material. One sample per animal was
performed using this method. The animals were monitored and given
buprenorphine
(0.02-0.05 mg/kg, s.c.) and a broad spectrum antibiotic upon awakening. The
analgesic
and antibiotic were administered 2 times per day for three days after surgery.
Blood was
drawn from each animal prior to euthanasia. The method used to draw blood was
as
follows: Acepromazine (1 mg/kg s.c.) was given to each animal to relax the
animal and
to dilate the vessels approximately 15-20 minutes before drawing the blood.
Next, a 23g
butterfly needle was placed in the central ear artery.
A vacutainer set up with 2 cc glass tubes was used to draw no more than 2 ml
of
blood from the animal. The needle was removed after the blood was drawn and
pressure
was placed on the vessel to allow for proper clotting. Furthermore, intra-
muscular
injections were administered during the surgical procedure while the animal
was under
full anesthesia. The soft tissue site was then shaved and prepped for
injections of type
10.0 PCA material. 3-5 injections into the lumbar muscle were made using a 16
gauge
hypodermic needle. 4 or 5 injections were given to the rabbits at 4, 7, and 14
day time-
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points to allow for PCA material recovery for chemical analysis. The remaining
time-
points had only 3 injections. Each injection contained approximately 0.2 grams
of the
PCA material. On the contralateral side, 3 injections were made of a
resorbable suture
material which acted as the positive control. The animals were euthanized by
intravenous
anesthesia with sodium pentobarbital followed by exsanguination by incision of
the
axillary arteries. For FTIR and XRD analysis, the PCA material was removed
from the
soft tissue implant sites, snap frozen in isopentane and stored in a -70 oC
freezer prior to
shipment to ETEX Corporation on dry ice. Soft and hard tissue test sites were
removed
and prepared for histology.
After euthanasia and exsanguination, tissues were removed from the animals,
embedded in paraffin, sectioned and stained with hematoxylin and eosin for
histopathological sections. Next, 300 mg of retrieved PCA material were
analyzed in a
Rigaku RU300 rotating-anode X-Ray diffractometer at the Center for Materials
Science
and Engineering facilities at the Massachusetts Institute of Technology in
Cambridge, MA
on January 22, 1997. A homogeneous mixture of 300 mg of KBr and 1.5 mg of
retrieved PCA material were analyzed by a Spectrum 1000 Perkin Elmer FTIR.
Also,
sections of tissue were scored for endosteal bone formation on a scale of 0 to
+3. Areas
with neutrophilic infiltrates generally had little osteoprogenitor or new bone
formation.
On a scale of 0 to +3, with 0 being no new endosteal bone formation and +3
being
extensive new endosteal bone formation, animals at day 4 had 0 to +1, those at
day 7
had +1, and at day 14 had + 2.
At day 4 and 7 there was visible, slight swelling over the defect site. Gross
findings at Day 14 displayed the development of a dome shaped bony callus over
the drill
site. There was an increased maturity of the bony callus at the defect site
for all test
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groups when evaluated at day 21, and a lack of any significant periosteal
reaction over the
remaining cortex. Microscopically, the defect site was filled with trabecular
and cortical
bone. There was a moderate amount of endosteal trabecular bone formation
around and
extending into the PCA material. At day 21 there was no indication of any
adverse
reaction to the implanted PCA material. Samples were retrieved at days 4, 7,
and 14 and
analyzed using XRD. See Figure _. These spectra confirmed the following: The
crystalline structure of PCA material is stable for at least 14 days in vivo,
and is
substantially the same as in vitro prepared PCA material. Additionally,
samples were
retrieved from animals at days 4, 7 and 14 and analyzed by FTIR. See Figure
The test material was chemically stable, and the reaction was completed in
vivo. PCA
material caused no unacceptable inflammatory response when implanted either
intramuscularly or in a bony defect site. Through XRD and FTIR analysis, PCA
material was determined to be chemically stable in vivo for up to 21 days
following
implantation.
Example 54: Quantification of Bone Healing with PCA Material
The Objective of this study was to quantify bone healing in the presence of
the
inventive PCA, and to monitor the resorption of the implanted PCA material.
The protocol was signed on February 14, 1996 and the study was performed at
Bio-Research Laboratories Ltd., 87 Senneville Rd., Senneville, Quebec, Canada,
H9X
3R3 in accordance with the United States FDA Good Laboratory Practice
Regulations (21
CFR Part 58). Surgeries were performed on February 15, 16, 22, 23, 29 and
March
1996 (for the 6 month study) and April 11 and 12, 1996 (for the 1-year study).
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Beagle dogs (canis familiaris), were obtained from HRP Inc., 6321 South 6th
Street, Kalamazoo, MI 49009 U.S.A.. The dogs were housed individually in
stainless-
steel cages each equipped with a bar type floor and an automatic watering
valve in 4
separate rooms. All animals had access to a standard certified pelleted
commercial dog
food (400 g- PMI Certified DogChow 5007: PMI Feeds Inc.) once daily and the
bowls
remained in the cages for approximately 24 hours (except during designated
procedures).
In addition, some animals occasionally received a diet supplement of canned
food, Mixit
or Canine ID (Hill's Science Diet). Municipal tap water was provided ad
libitum.
The PCA material was supplied as a sterile powder in pre-measured packages.
The
material was prepared on the day of surgery for implantation. The material was
hydrated
with appropriate amounts of sterile water and stored covered at room
temperature prior to
implantation. Each dog received a dose of Penlong-XL (Benzathine penicillin G
and
Procaine penicillin G) (1 mL) intramuscularly at least 1 hour prior to surgery
and again 2
days following surgery. Each animal was pre-anesthetized with an intramuscular
injection
of AC-Promazine (0.05 mg/kg), Butorphanol (0.2 mg/kg) and Glycopyrrolate (0.01
mg/kg) at least 10 minutes prior to presurgical preparation. The animals were
then
prepared for surgery by shaving one (Group 1 and 2) or both (Groups 3 and 4)
hindlimbs
from the pelvis to the lower leg. The shaved area was washed with HibitaneTM
(Chlorhexidine gluconate 4%) followed by a liberal application of 70%
isopropanol and
BetadineTM (Povidone iodine 10%). The animals were anesthetized with an
intravenous
injection of thiopentone sodium 2.5% and the subcutaneous injection site (mid-
dorsal
thoracic region) for Group 2 was prepared in the same manner. Prior to
surgery,
DuratearsTM ointment was administered to each eye. All animals were intubated
and
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maintained under isoflurane anesthesia for the surgical procedure. Lactated
Ringer's (at a
rate of 10 mL/kg/hour) was administered perioperatively.
A longitudinal skin incision was made along the lateral surface of the
hindlimb to
expose approximately 8-10 cm of the femur. The periosteum overlying the femur
was
reflected from the bone. A template (measuring 6 cm) was applied identifying
the sites
for the holes which were drilled at either end of the shaft. Using an
appropriately sized
drill bit, a piece of bone approximately 3-5 mm deep was removed from each end
of the
shaft and using an oscillating saw, this hole was elongated distally for
approximately 4-5
cm. The marrow was removed and any significant bleeding was appropriately
controlled.
For Group 1 animals, following creation of the defect site, the bone removed
was cut into
small pieces, rinsed with saline and packed into the defect site as the
autologous bone
application. For Group 2 animals, following creation of the defect site the
bone substitute
material was placed into the defect site, ensuring that no excess amount of
material was
left in the surrounding tissues. Following this procedure, a quantity of a_
_BSMTM (to
make up 25 g, total dose) was injected subcutaneously in the mid-dorsal
thoracic region.
In the case of Group 3 and 4 animals, following creation of the defect site on
the first
hindlimb, the bone substitute material was placed into the defect site,
ensuring that no
excess amount of material was left in the surrounding tissues. The bone
removed was cut
into small pieces and rinsed with saline. A defect site was created in the
opposite limb
and the prepared bone was placed in the site. Each defect site was marked by
placing a 1
mm piece of K-wire at each end of the groove. The fascia was then sutured
closed with
resorbable suture to ensure the material remained in place. The surgical site
was closed
with surgical staples and the staples were removed approximately 10 days after
surgery.
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Radiography was performed on both hindlimbs of each animal from Group 3 on
the day of necropsy for Week 0, and on all surviving Group 3 animals in Week
3, 12 and
26. Animals were sedated for the procedure. The animals were euthanized by
intravenous anesthesia with sodium pentobarbital followed by exsanguination by
incision
of the axillary arteries. The tissues indicated above were prepared by
embedding in
paraffin wax, sectioning and staining with hematoxylin and eosin. Half of each
femoral
implantation site (Groups 1, 2 and 4) was prepared as a decalcified section
and prepared
as hematoxylin and eosin and Masson's trichrome stained slides. The remaining
half of
each site was retained in 70% alcohol and prepared as an undecalcified section
(in
appropriate embedding media) and stained with von Kossa and Goldner's
Trichrome while
fixed in Zenker's fluid.
Following histopathology analysis, histomorphometric analysis was performed.
Defect boundaries were determined subjectively and total area of bone and the
PCA
material present were tabulated for the region of the defect. Histomorphometry
confirmed and extended the histopathology. Histomorphometric data from all von
Kossa
stained undecalcified sections, for all available experimental groups were
pooled at each
time point according to implant type independent of whether the animals were
from group
1, 2 or 4. Results for new bone formation in both PCA material and autograft
treated
defects, as well as PCA material resorption, and are presented in Figure _.
New bone
formation in autograft recipients appeared to occur slightly in advance of new
bone
formation in PCA material recipients. At four weeks new bone in autograft
recipients
reached a near maximum value of 74.7% +/-20 ( sem; n=8). By week 26 autograft
values had decreased to 56.78% +/-20.9 (sem; n=4) suggesting that increased
remodeling was occurring perhaps due to failure of some graft regions. While
new bone
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did not reach its maximum value (77.18% +/-11.2, sem; n = 8) until week 12 in
the
PCA material recipients, the apparent remodeling observed in autografts at 26
weeks was
not observed in the PCA material recipients. The PCA material values at week
26 (78%
+/- 21.5, sem; n=4) were comparable to the 12 week values. Observable residual
PCA
material represented less than 95 % of the entire surface area in the defect
by week 4 and
less than 0.3% by week 26. Since the defect was originally 100% filled with
PCA
material, resorption was greater than 99% by week 26.
Other Embodiments
It will be understood that the foregoing is merely a description of certain
preferred
embodiments of the invention and is not intended to be limiting thereof. The
following
claims cover all of the generic and specific features of the invention herein
described in
the text and accompanying drawings.
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